Centrifuge and Separation Vessel Therefore

ABSTRACT

The centrifugation vessel includes an outer wall containing an interior space. A dam defines a barrier which divides the interior space into at least two regions including a catch basin defining a higher gee region and a reservoir defining a lower gee region. These regions are joined together over the dam. The dam includes a face which is preferably tapered to enable optimization of speed of separation of a sample placed within the vessel. The vessel is usable in a biological sample processing method by having the higher gee region of the vessel configured to have an elongate form and the volume optimized for collection of a higher density fraction of the sample. Supply and withdrawal tubes extend into the regions for reliable extraction and separate collection of differing density fractions after separation by centrifugation.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims benefit under Title 35, United States Code§119(e) of U.S. Provisional Application No. 61/401,877 filed on Aug. 21,2010.

FIELD OF THE INVENTION

The following invention relates to centrifuges and vessels thereforewhich are used in processes for separating a sample into fractions ofdifferent densities. More particularly, this invention relates tocentrifuges and centrifuge operation methods which utilize samplecontaining vessel geometry to speed the sample separation process andmaintain separation after centrifugation.

BACKGROUND OF THE INVENTION

Essentially a centrifuge is an apparatus that separates particles thatare in a fluid. Centrifugation provides a means for achieving two goalsthrough one approach: particles can be both concentrated and purifiedunder centrifugal forces. Centrifugation of particles in a suspendingmedium causes the particles to sediment rapidly in the direction outwardfrom the center of rotation. The centrifugal force generated bycentrifugation is proportional to the speed of rotation and the radiusof the rotor. At a fixed centrifugal force and medium viscosity, thesedimentation rate of the particle is proportional to the molecularweight of the particle and the difference between its density and thedensity of the medium. There are two types of centrifugation procedures:one is “preparative” which is used to isolate specific particles; theother is called “analytical” which is used to measure the physicalproperties of sedimenting particles. When a suspension is rotated at acertain speed or revolutions per minute (RPM), centrifugal force causesthe particles to move radially away from the axis of rotation.

Centrifuges are among a select group of laboratory instruments that areas scalable as they are configurable. Individuals who have used benchtop centrifuges that handle sub-milliliter volumes may be surprised tolearn that centrifuges, some as large as rooms, are used in industrialprocessing. The use of centrifuges has been summarized in the followingbooks, the entire contents are incorporated herein: CentrifugalSeparations in Biotechnology by Wallace Woon-Fong Leung Academic Press;1 edition (Aug. 30, 2007) (by reference and for industrial applicationsreviewed in Perry's Chemical Engineers' Handbook 8/E Section18:Liquid-Solid Operations and Equipment McGraw-Hill Professional (Aug.1, 2007); Industrial Centrifugation Technology by Wallace Woon-FongLeung (Feb. 1, 1998); Biological Centrifugation (The Basics) by J. M.Graham (Oct. 15, 2001); Refining iron-contaminated zinc by filtrationand centrifugation by John A. Ruppert (Jan. 1, 1967); Processing byCentrifugation by Liya L. Regel and William R. Wilcox (Sep. 1, 2001);Centrifugation in Density Gradients by C. A. Price (October 1982);Decanter Centrifuge Handbook by A. Records and K Sutherland (Mar. 16,2001); Bioseparations Science and Engineering (Topics in ChemicalEngineering (Oxford University Press) by Roger G. Harrison, Paul W.Todd, Scott R. Rudge, and Demetri Petrides (Oct. 31, 2002).

Centrifuge designs are simple, consisting of an enclosed compartmentinside which a rotor spins rapidly. Rotors, which can usually beinterchanged, contain equally spaced openings into which sample tubesare inserted. Samples will either spin at a fixed angle relative to therotating axis or “swing out” to perpendicular under centripetal force asthe rotor speed increases. Forces generated as the rotor spins causecomponents in the sample to migrate toward the bottom of the sampletube, according to weight or density.

Entry-level mini-centrifuges easily fit on a bench top, operate at asingle, relatively low speed, generate low gravitational (g) forces, andcost only a few hundred dollars. “Minis” are used for samples whosecomponents are easily separated by density. Most medical and veterinaryoffice centrifuges are of this type. The next level up, compact benchtop centrifuges, spin tubes of up to about 2 mL and create tens ofthousands of gs. Researchers use them to separate DNA, proteins, andcellular components.

There are many ways to differentiate centrifuges by type, speed, andfeatures. Beckman-Coulter (Fullerton, Calif.), for example, divides itsproduct line into three basic platforms: bench top devices operating atup to about 10,000 rpm, “washing machine” centrifuges that provide up toabout 100,000 g, and ultracentrifuges that deliver in excess of onemillion g. In fact, one could argue that all centrifuges exist along acontinuum of features that may be mixed and matched, which includeg-force generated, sample tube size, refrigeration capabilities,rotation angle, computerization, and others. The ultracentrifuge is acentrifuge optimized for spinning a rotor at very high speeds, capableof generating acceleration as high as 1,000,000 g (9,800 km/s²). Thereare two kinds of ultracentrifuges, the preparative and the analyticalultracentrifuge. Both classes of instruments find important uses inmolecular biology, biochemistry and polymer science.

Common Centrifugation Vocabulary and Formulas.

-   Pellet: hard-packed concentration of particles in a tube or rotor    after centrifugation.-   Supernatant: The clarified liquid above the pellet.-   Adapter: A device used to fit smaller tubes or centrifugal devices    in the rotor cavities.-   RPM: Revolutions Per Minute (Speed).-   R_(max): Maximum radius from the axis of rotation in centimeters.-   R_(min): Minimum radius from the axis of rotation in centimeters.-   99999: Relative centrifugal Force. RCF=11.17×Rmax (RPM/1000)²-   K-factor: Pelleting efficiency of a rotor. Smaller the K-factor,    better the pelleting efficiency.

$K = \frac{2.53 \times 10^{11}{{Ln}\left( {R_{{ma}\; x}/R_{m\; i\; n}} \right)}}{({RPM})^{2}}$

-   S-value: the sedimentation coefficient is a number that gives    information about the molecular weight and shape of the particle.    S-value is expressed in Svedberg units. The larger the S-value, the    faster the particle separates.

The force on the particles (compared to gravity) is called RelativeCentrifugal Force (RCF). For example, an RCF of 500×g indicates that thecentrifugal force applied is 500 times greater than Earth'sgravitational force. Modern day ultracentrifuges can generate forces inexcess of 300,000 times that of gravity, forces sufficient to overcomethe very cohesion of most molecules (including the metal of the rotor).The force is usually given as some value times that of gravity (g) andis called RCF. The centrifugal force is dependent upon the radius of therotation of the rotor, the speed at which it rotates, and the design ofthe rotor itself (fixed angle, vs swinging bucket). Rotor speed anddesign can be held constant, but the radius will vary from the top of acentrifuge tube to the bottom. If a measurement for the radius is takenas the mid-point, or as an average radius, and all forces aremathematically related to gravity, then one obtains a relativecentrifugal force, labeled as ×g. Centrifugation procedures are given as×g measures, since RPM and other parameters will vary with theparticular instrument and rotor used. Relative Centrifugal Force is aconstant that is independent of the apparatus used.

Protocols for centrifugation typically specify the amount ofacceleration to be applied to the sample, rather than specifying arotational speed such as revolutions per minute. This distinction isimportant because two rotors with different diameters running at thesame rotational speed will subject samples to different accelerations.During circular motion the acceleration is the product of the radius andthe square of the angular velocity and it is traditionally named“relative centrifugal force” (RCF). The acceleration is measured inmultiples of “g” (or ×“g”), the standard acceleration due to gravity atthe Earth's surface, and it is given by

${RCF} = \frac{{r\left( {2\pi \; N} \right)}^{2}}{g}$

where

-   g is earth's gravitational acceleration,-   r is the rotational radius,-   N is the rotational speed, measured in revolutions per unit of time.-   This relationship may be written as

RCF=1.118×10⁻⁵ r _(cm) N _(RPM) ²

where

-   r_(cm) is the rotational radius measured in centimeters (cm),-   N_(RPM) is rotational speed measured in revolutions per minute    (RPM).

In 1851, George Gabriel Stokes derived an expression, now known asStokes' law, for the frictional force, also called drag force, exertedon spherical objects with very small Reynolds numbers (e.g., very smallparticles) in a continuous viscous fluid. Stokes' law is derived bysolving the Stokes flow limit for small Reynolds numbers of thegenerally unsolvable Navier-Stokes equations:

F_(d)=6πμRV

where:

-   -   F_(d) is the frictional force acting on the interface between        the fluid and the particle (in N),    -   μ is the fluid's viscosity (in [kg m⁻¹s⁻¹]),    -   R is the radius of the spherical object (in m), and    -   V is the particle's velocity (in m/s).

If the particles are falling in the viscous fluid by their own weightdue to gravity, then a terminal velocity, also known as the settlingvelocity, is reached when this frictional force combined with thebuoyant force exactly balance the gravitational force. The resultingsettling velocity (or terminal velocity) is given by:

$V_{s} = {\frac{2}{9}\frac{\left( {\rho_{p} - \rho_{f}} \right)}{\mu}g\; R^{2}}$

where:

-   -   V_(s) is the particles' settling velocity (m/s) (vertically        downwards if p_(p)>p_(f), upwards if p_(p)<p_(f)),    -   g is the gravitational acceleration (m/s²),    -   p_(p) is the mass density of the particles (kg/m³), and    -   p_(f) is the mass density of the fluid (kg/m³).

From application of Stoke Law, the following principles are derived: Thesedimentation rate of particles is proportional to their size; thesedimentation rate is proportional to the density of the particle and tothe medium; the sedimentation rate is null when both densities are thesame; the sedimentation rate diminishes by increasing the viscosity ofthe medium, and the sedimentation rate increases by increasing the forcefield.

Separation methods. Centrifugal separations can be separated into twobasic types: differential pelleting and zonal separations. Differentialpelleting is most useful for crude separations of raw material wherepurity and yield are not critical. The method involves sedimentingparticles out of solution, and either retaining the pellet orsupernatant depending on where the material of interest is located. Aspredicted by the equations above, larger particles will sediment priorto smaller ones, and more dense particles prior to less dense ones. Inaddition, asymmetrical particles will sediment more slowly thanspherical ones of the same mass and density. The separations are notclean, however, since the centrifugal force required to pellet largeparticles from the top of a sample will also pellet small particles fromthe bottom. The greater the difference in sedimentation rate between theparticles being separated, the cleaner the preparation will be.

Differential centrifugation. In this method, the centrifuge tube isfilled with an uniform fluid mixture. After centrifugation are obtainedtwo fractions: a pellet that contains the sedimented material and asupernatant with the material not sedimented. The method is nonspecific,and it is difficult to assure if the desired particle will remain in thesupernatant, in the pellet or distributed between both; but is a veryuseful technique. An example of the application is the the eliminationof prokaryotic cells in culture broths. Centrifugation of cultures to10.000×g for 20 minutes is enough to create the required centrifugalforce necessary to sediment bacteria cells.

Protein precipitation with ammonium sulfate. The saline precipitation isa technique used in the initial steps of enzyme purification and in someimmunoassays. Proteins are surface polyelectrolytes, when a salt isadded to the medium, their ions neutralize the protein charges, arrivingat a situation in which there aren't net charge, then, proteinsflocculate. This technique requires differential centrifugation:centrifuge to 10,000×g for 60 minutes so that the proteins that areflocculating are precipitated.

Thermal treatment. Some proteins are more thermostable than others whichcan be used as a method for isolating and concentrating. The denaturedproteins tend to become aggregated and by using differentialcentrifugation can be eliminated by their sedimentation.

Zonal Separations. There are two types of zonal separations, both ofwhich rely on density gradients: rate zonal and isopycnic. Rate-zonalcentrifugation separates particles based on differences in theirsedimentation coefficients (s), which is a function of both particlesize and density. In practice, differences in size dominate thedifferences in sedimentation velocity (s) among most biologicalparticles, since the range of densities is not large and s varies as thesquare of particle diameter. Isopycnic separations discriminate amongparticles based solely on differences in buoyant density. In bothtechniques, centrifugation is carried out in a density gradient, which,among other functions, prevents mixing of the sample thereby ensuringthat separated particles remain separated.

For rate zonal separations, a sample is introduced to the top of adensity gradient. When subjected to centrifugal force, the samplecomponents migrate through the gradient according to their s. Particlesmigrate at different speeds, resulting in greater distance betweenparticles having different s over time. Because the particles do notcome to rest at equilibrium in the gradient, care must be taken so thatthe particles of interest do not pellet. For effective separations, theinitial sample volume should be small (the sample layer should be only afew millimeters thick), because the sample zone continues to widen overtime as a result of diffusion. Therefore, while rate zonal gradientseliminate problems associated with pelleting during the purification, asuitable concentration step that does not result in pelleting oraggregation must be employed prior to using this technique. Manydifferent types of density gradient media may be employed for rate zonalseparations. Choosing the appropriate medium requires matching theproperties of the medium to one's specific application. In general, itis beneficial to employ media preparations of high viscosity for ratezonal separations because viscous forces will magnify differences insettling velocity between similar particles.

In isopycnic (or equilibrium buoyant density) separations, particlesmigrate through the density gradient until they reach the point at whichtheir density is equal to that of the surrounding medium. Media used forthis type of separation must therefore be able to form a solution thatis at least as dense as the particle that are to be purified. Samplesmay be top-loaded or bottom-loaded in preformed density gradients, orhomogeneously mixed with a self-forming gradient medium beforecentrifugation. As particles approach their equilibrium position in agradient, the difference in density between the particle and the mediumdecreases and, consequently, so does the migration rate of the particle.Particles become increasingly focused over time until the focusing forceis balanced by diffusion. Achieving equilibrium, at which point theparticles are most focused, can require long centrifugation runs underhigh g-forces. This method eliminates pelleting and aggregationconcentrated and purified target particle preparations at the same time.Isopycnic separations also provide a means for directly determiningbuoyant density, a commonly reported physico-chemical property ofmaterials.

Because the two zonal techniques described above separate based onpartially independent properties (size versus density), they can be usedsequentially to separate particles that may not be separable by eithermethod alone. Two-dimensional separations have been particularlyvaluable for biological particulate purification, since most biologicalparticulates have a combination of sedimentation coefficient and buoyantdensity that distinguishes them from other fluid constituents.

Density gradient centrifugation. Density gradient centrifugation is apopular method for fractionation of nucleic acids, virus particles andproteins. This is done by centrifugation of a mixture of particles orcomponents in a density gradient column. Particles or components withdifferent densities will be separated at different positions in thedensity gradient column. Basically, there are two types of densitygradient centrifugation, termed rate zonal and isopycnic. Preparation ofdensity gradients. In either zonal or isopycnic density gradientcentrifugation, a density gradient has to be prepared prior tocentrifugation by either a hand-layering process or by employing adensity gradient former. A number of materials such as sucrose, Ficoll,or salts such as NaCl, NaBr, or CsCl, can be used for preparation of thedensity gradient. A sucrose density gradient can be prepared bypipetting into a centrifuge tube layers of progressively lowerconcentrations of sucrose on top of higher concentrations. Densitygradient columns can also be prepared by the use of a syringe with apiece of tubing attached to the syringe needle (20-22 gauge). To preparea 5-20% sucrose density gradient in a 15 ml tube, start by placing 3 mlof 5% sucrose in the tube and then carefully inject the 3 ml of 10%sucrose into the tube by keeping the tip of the syringe tubing at thebottom of the centrifuge tube. Repeat the process with 3 ml of 15% and 3ml of 20% sucrose. When the preparation is completed, remove the syringetubing carefully by holding the tip of tubing against the wall of thecentrifuge tube. Ficoll and cesium chloride density gradients can beprepared in a similar manner. Density gradients thus prepared can eitherbe used immediately as a step gradient or made into a linear gradient byallowing it to diffuse in a refrigerator overnight.

Rate Zonal Density Gradient Centrifugation. In rate zonal densitygradient centrifugation, a sample solution containing particles to befractionated is layered on top of the density gradient column. Undercentrifugation the particles will start to sediment through the densitygradient into separate zones. Each zone consists of particles with thesame sedimentation rate. In the rate zonal centrifugation,centrifugation must be terminated before any of the separated zonesreach the bottom of the tube, since the density of some zones may behigher than the highest density area in the density gradient.

Isopycnic (=“same density”) density gradient centrifugation. Inisopycnic density gradient centrifugation, the density gradient columnencompasses the whole range of densities of sample particles. Eachparticle will sediment only to the position in the gradient where thedensity in the gradient column equals its own density, and the particlewill remain at this position. In the isopycnic method, it is not alwaysconvenient to form a gradient artificially and layer the sample on topof the gradient column. It is sometimes necessary to start with auniformly-mixed solution of gradient material and sample. Duringcentrifugation, gradient material redistributes in the tube and forms alinear density gradient. At the same time, sample particles which areinitially distributed throughout the tube either sediment or float totheir isopycnic positions. This type of procedure is termed theself-generating gradient technique.

Historically, self-generating isopycnic density gradient centrifugationhave generally required long hours of centrifugation. For example,isopycnic “banding” of DNA can take 36-48 hours in a self-generatingcesium chloride density gradient using standard swinging-bucket orfixed-angle ultracentrifuge rotors. The running time cannot be shortenedby increasing the rotor speed, since this only results in changing thepositions of zones in the tube due to the redistribution of gradientmaterial further down the tube. Run times can be decreased by shorteningthe distance over which the gradient forms, however. A recent innovationto decrease running times for DNA preparation (down to 3-4 hours) hasbeen the use of “vertical” or “near-vertical” rotors, in which thegradient forms across the diameter, rather than the length of the tube.

Separated zones (“bands”) from both rate zonal and isopycnic densitygradient centrifugation can be removed by: (i) puncturing a hole on thebottom of the tube and collecting the fractions or drops either manuallyor using a fraction collector, (ii) removing successive zones from thetop of the unpunctured tube, or (iii) puncturing the tube through theside to recover a band as a single fraction.

Application of Density Gradient Centrifugation. Density gradientcentrifugation has been used extensively in separation and purificationof a wide variety of biological materials. It is particularly wellsuited for the study of viruses and nucleic acids. Cells andsub-cellular components such as bacteria, nucleoids, ribosomes,membranes, etc. have been isolated and purified with this technique.

Numerous investigators have identified the criteria for choosing densitygradient media for biological separations (Cline and Ryel 1971; Hintonet al. 1974). In summary, the criteria are as follows: The media shouldbe inert or at least nontoxic to the specimen (minimal osmotic effect,ionic strength, and neutral pH); the media should form a solutioncovering the density range for the particular application, and be stablein solution; the physical and chemical properties of the media should beknown, and it be possible to use one or more properties to determine theprecise concentration of the media; the solution should not interferewith monitoring of zones of fractionated material within the gradient;it should be easy to separate the sample from gradient material withoutloss of the sample or its activity; and the gradient media should beavailable as a pure compound; and be relatively inexpensive.

Ionic media. Alkali metal salts, such as cesium chloride, are mostwidely used for making isopycnic gradients with any standard techniqueincluding preformed or self-forming gradients. Metal salts can providesome of the densest preparations available, have a low viscosity, andtheir concentration in solution is easily measured by refractive index.The major drawbacks of alkali metals lie in their effects on biologicalactivity; salt solutions have high ionic strengths, which disruptprotein-protein and nucleic acid-protein bonds, and have highosmolarities, affecting particle hydration.

Small hydrophilic organic molecules (sucrose, glycerol, sorbitol, etc.)that non-ionic media. Sucrose meets most of the criteria of an idealmedium for rate zonal separations, being biologically inert, stable, andrelatively cheap. Due to its popularity as such, sucrose is very wellcharacterized with respect to concentration, viscosity, density, andrefractive index, making it easy to develop and adapt methods foruncharacterized particulates. While sucrose has little effect onintermolecular bonding and is non-ionic, high osmotic pressure may causeshrinkage in enveloped viruses and thereby affect infectivity insensitive viruses. The high viscosity of sucrose at concentrationsuseful for virus separations may aid in separation between similarlysized particles under rate zonal conditions, but the high viscosity andrelatively low density limits the application of sucrose and other smallorganic molecules in isopycnic separations of viruses. Other sugars,notably glycerol and sorbitol, have also been used effectively as ratezonal media. These gradients need to be preformed as solutions of smallorganic molecules do not generally form gradients when centrifuged.

High molecular-weight organics (Ficoll, dextran, glycogen, etc.). Highmolecular-weight polysaccharides do not penetrate intact biologicalmembranes and have a lower osmolarity than solutions of monosaccharides.Therefore, these media may be especially useful when employed withbiological particles. Unfortunately, due to the size of thesepolysaccharides, they cannot be removed from the sample by dialysis orultrafiltration, so dilution and high-speed centrifugation are generallyrequired, which are contraindicated with sensitive specimens asdiscussed above. Since polysaccharide media such as Ficoll (GEHealthcare) and dextran diffuse slowly, it is necessary to preformlinear gradients using gradient mixers. This characteristic also ensuresthat gradients are quite stable once formed. The high viscosity of thesemedia necessitates longer spin times than those of sucrose gradients.

Colloidal Silica (Percoll, Ludox, etc.). Colloidal silica suspensionssuch as Percoll (GE Healthcare) and Ludox (DuPont) are truly non-ionicmedia that can be used to rapidly generate self-forming gradients. Thesemedia are well characterized, permitting the use of refractive index forexamining density profiles of gradients since absorption prohibitsmonitoring by UV light. Percoll density marker bead kits, available froma number of vendors (e.g., Sigma-Aldrich, product DMB-10), are usefulfor visually monitoring gradient profiles. Whereas colloidal mediacannot be effectively filter sterilized, they may be autoclaved beforebeing adjusted for osmolarity and can be used over a wide pH range(5.5-10 for Percoll). Percoll is commonly used for cell separations,because the suspension of colloidal silica can be prepared in almost anybuffer required to maintain cell viability. Another limitation is thatthe silica particles may begin to pellet before smaller viruses havetime to form discrete, purified bands. To remove Percoll from viruspurifications requires dilution and high-speed differentialcentrifugation (i.e., 100,000 g for 2 h in a swinging bucket or 1.5 h inan angled rotor), which may lead to aggregation and deactivation ofviruses, as previously discussed.

Iodinated organic compounds (Nycodenz, OptiPrep, and metrizamide).Iodinated compounds provide an excellent combination of biologicalinertness, a wide density range, and low viscosity, which allows forreduced spin times. These compounds, including Nycodenz (Axis-Shield),iodixanol (sold as OptiPrep by Axis-Shield), and metrizamide, are heatstable, autoclavable, and of minimal ionic strength.

In U.S. Pat. No. 5,605,529 entitled “HIGH EFFICIENCY CENTRIFUGE ROTOR”issued on Feb. 25, 1997 to Petithory, the entire contents areincorporated herein by reference, disclosed about the uses of fixedangular rotors in centrifuges. The field of the Petithory invention wasrelating generally to centrifuge rotors, and more particularly to fixedangle centrifuge rotors.

Most blood chemistry tests require preparation of serum or plasma priorto analysis. To this end, red blood cells and other cellular materialare separated from the patient's blood following collection. Typically,blood is collected in evacuated tubes and centrifuged at 2000-3000 rpmfor 10-20 15 minutes.

One type of centrifuge rotor which houses tubes for centrifugation is afixed angle rotor, in which the tubes are retained in cavities angledrelative to the axis of rotation. The dynamics of fixed angle rotors andtheir ability to enhance the speed of centrifugation are known in theart. The clearing efficiency (K-factor) of fixed angle rotors, whichcorresponds to the time required to sediment a specific particle in aknown medium at a given speed of rotation, can be calculated using thefollowing formula:

${K\text{-}{factor}} = \frac{2.53 \times 10^{11} \times {{Ln}\left( \frac{r_{1}}{r_{2}} \right)}}{N^{2}}$

where r₁=radius, in cm, from the outermost point of liquid in the tubeto the central axis of rotation, r₂ radius, in cm, from the center ofthe top of liquid within the tube to the central axis of rotation andN=rpm.

It is apparent from the above formula that a rotor having tube cavitiesinclined at a steep angle (approaching 0° in reference to the axis ofrotation) can provide the lowest K-factor, and the greatest separationefficiency. However, there are drawbacks associated with using a rotorhaving steeply angled tube cavities including the fact that the steeperthe angle, the greater the tendency of particles to adhere to theoutermost wall of the tube, which could lead to contamination of thesupernatant.

Another drawback is that the sedimentation boundary formed in a fixedangle rotor centrifuge device is significantly larger than thesedimentation boundary formed in centrifuges using a swing-out stylerotor.

Another disadvantage of a steeply angled rotor occurs when gel barriertubes are used. The position of the gel band along the top side-wall ofthe processed tube makes it difficult to pipette the supernatant plasmaor serum without coming into contact with the gel material. This isespecially important in analyzers which employ primary tube samplingcapability. Since the thickness of the gel band decreases with therelative steepness of the tube angle, the band can collapse upondeceleration and cause contamination of the supernatant with theparticles in the gel.

Still another disadvantage is that there exists a “mixing effect” duringreorientation of the tubes from the horizontal position to the verticalposition during deceleration, which also increases with the steepness ofthe tubes within the rotor. During sedimentation, particles traveloutward from the axis of rotation until they hit the wall of the tube,then slide downward along the tube wall. This descending layer ofincreased particle concentration combined with a corresponding ascendinglayer of reduced concentration fluid creates a fluid flow within thetube which increases the time required to sediment particles,particularly those of low density or irregular shape.

A final disadvantage of using steeply angled tube cavity rotors is thatas the steepness of the tube increases, the capacity of the tubedecreases. Since the closure of these tubes can trap particles, there isa limit to the tube angle that can be used during centrifugation.

Advances in the speed of test instrumentation have created a demand forfaster blood separation methods, and particularly for high speedseparation of the blood or serum within the original blood collectiontube while maintaining a minimal distortion of the separation boundarywithin the sample containers.

Centrifuges are suited and used for the separation of componentsincluding cells, organelles or macromolecules contained in biologicfluids including bone marrow, peripheral blood, urine, phlegm, synovialsemen, milk, saliva, mucus, sputum, exudates, cerebrospinal fluid,amniotic fluid, cord blood, intestinal fluid, cell suspensions, tissuedigests, tumor cell containing cell suspensions, microbe containing cellsuspensions, radiolabelled cell suspensions and cell culture fluid fortherapeutic or diagnostic purposes. Centrifuges are well suited for thewashing of cell suspensions and other particulate matter. Centrifugesalso are used for separation of components present in aqueous solutions,lake water, ocean water, river water, waste water, and sewage for thepurpose of preparative analytical testing or purification. Centrifugesare also suited for the separation of a component of an inorganic ororganic chemical reaction that has resulted in the formation of aprecipitate or flocculent. Centrifuges have occasionally been used forseparation of particulates added to an aqueous solution for the purposeof inducing a chemical reaction and then terminating said chemicalreaction by centrifugation of the heterogeneous fluid using theapparatus of the invention. Centrifuges have been used to in combinationwith density particles to perform immunoaffinity cell separation steps.This expansive list is still not inclusive for all the varied functionsfor which centrifuges are routinely employed and known in the prior art.Below are detailed examples of some of these applications.

Charlton et al. were awarded U.S. Pat. No. 4,106,907 on Aug. 15, 1978entitled “Centrifuge Tube and Method for Performing Assay with Same”,for which the entire contents are incorporated herein by reference forthe purpose of handling radioactive material.

Kimura was awarded U.S. Pat. No. 4,861,477 on Aug. 29, 1989 entitled“Tubular Container for Centrifugal Separation” for which the entirecontents are incorporated herein by reference. A tubular container forcentrifugal separation suited for easy separation of a relatively smallamount of the phase having an intermediate specific gravity from theheaviest and lightest phases. The container has a first section defininga bottom chamber of a certain volume for containing therein the heaviestphase, a second section contiguous to the first section and defining anintermediate chamber for containing therein the phase having theintermediate specific gravity, and a third section contiguous to thesecond section and defining an upper chamber for containing therein thelightest phase. The diameter of said second section is smaller than thediameters of the first and third sections.

Saunders et al. was awarded U.S. Pat. No. 5,422,018 on Jun. 6, 1995entitled “Centrifuge Tube and Adaptor” for which the entire contents areincorporated herein by reference. Saunder's discloses a centrifuge tubeand adaptor apparatus is provided which facilitates separation ofbiological materials and permits easy extraction of a fraction aftercentrifugation. The tube is a deformable tube with a wide upper chamberand a narrowed lower portion. The tube is supported within thecentrifuge rotor or within another container within the centrifuge by aliquid support medium, which surrounds and supports the narrow portionof the tube, and thus prevents the tube from collapsing during highspeed centrifugations.

Muller was awarded U.S. Pat. No. 5,260,032 on Nov. 9, 1993 entitled“Integral Centrifuge Tube and Specimen Slide” for which the entirecontents are incorporated herein by reference. Muller's device was madefor use in a centrifuge to automatically prepare microscope slidespecimens from samples of body fluids. A centrifuge tube and specimenslide are formed integrally in a unitary device. A lens clearancesection is provided as a planar surface to avoid interference betweenthe device and the rotatable lenses of a turret microscope while thedevice is in viewing position on the microscope stage. The device isconstructed to minimize packing of sediment and other constituentelements of the sample at the entrance to the slide member and is soconfigured as to admit of a step during the centrifuge process whichflexes the slide member to enhance the distribution of cells depositedtherein.

Levine et al. were awarded U.S. Pat. No. 5,342,790 on Aug. 30, 1994entitled “Apparatus for Indirect Fluorescent Assay of Blood Samples” forwhich the entire contents are incorporated herein by reference. Levinediscloses that a patient's health is diagnosed by centrifuging bloodsamples in a transparent tube, which tube contains one or more groups ofparticles such as lyposomes or plastic beads of different densities foreach group. Each group of density-defined particles carries antigens orantibodies which are specific to a complement antigen or antibody whichmay be in the blood sample being tested, and which are indicative of thepatient's health. A label tagged antibody which is specific to all boundantibody/antigen couples is added to the blood sample so as to formlabeled antibody+antigen−antibody complexes (AAAC) in the blood sample.Upon centrifugation, the complexed particles will settle out indifferent areas in the tube according to the respective density of theparticles, and the degree of label emission of the particle layers canenable qualitative or quantitative analyses of the blood sample to bemade. Unbound labeled antibodies will be washed away from the complexedlayers by the washing action of the descending blood cells during thecentrifugation step. Unbound labeled antibodies will thus not interferewith the analysis.

Gerken was awarded U.S. Pat. No. 4,713,219 on Dec. 15, 1987 entitled“Plastic Reaction Vessel” for which the entire contents are incorporatedherein by reference. Gerken describes a plastic reaction vessel forholding a small quantity of liquid comprises a vessel body which has abody flange (4) surrounding an opening formed in the body, a cover, anda connecting strip (5) which is integral with the vessel body and thecover. Opposite to the connecting strip (5), the body flange (4) has adownwardly facing abutment surface (25), which is engageable by ahooklike extension (23), which is formed on the cover (6) and extendsdownwardly when the cover is closed. The connecting strip (5) comprisesa hinge portion (12) between its opposite end portions. The covercomprise a cylindrical skirt, which is adapted to be inserted into thevessel body through the opening therein. A sealing lip (8) is providedon the outside of said skirt at that end thereof which is adapted to beinserted into the opening of the vessel body. The cover (6) has anoutwardly protruding rim (16), from which a depending flange extends,which contacts the body flange so that a parallel guidance of the cover(6) is effected in conjunction with the hinge portion of the connectingstrip. An alignment of the cover (6) is effected by the sealing lip (8),which is formed on the cylindrical skirt and in sealing contact with theinside surface of the vessel body.

According to Kaiser (U.S. Published Patent Application No. 2004/0038316A1) the improved methods of separating cells have had a great utility inthe many medical and biological fields that require purifiedpopulations. Many biological techniques such as are employed inbiotechnology, microbiology, clinical diagnostics and treatment, invitro fertilization, hematology and pathology, require such processes asidentification, separation, culturing, or manipulation of a target cellor particle, e.g. cell subsets, platelets, bacteria, virus particles,etc. Cell separation is a rapidly growing area of biomedical andclinical development. Improved methods of separating a desired cellsubset from a complex population permit the study and use of cells thathave relatively uniform and denned characteristics. Cell separation iswidely used in research, e.g. to determine the effect of a drug ortreatment on a targeted cell population; investigation of biologicalpathways; isolation of transformed or otherwise modified cellpopulations; etc. Present clinical uses include the isolation ofhematopoietic stem cells for reconstitution of blood cells, particularlyin combination with ablative chemo and radiation therapy.

The disclosure of an invention in U.S. Published Patent Application No.2004/0182795, by Randel Dorian and Richard Storrs, the entire contentsof which are hereby incorporated herein by reference incorporated hereinby reference., teaches an apparatus and methods for separation andconcentration of plasma and plasma platelet mixtures from plasmaerythrocyte mixtures such as whole blood and is particularly applicableto the preparation and use of autologous plasma concentrates.

Rapid fractionation of blood into erythrocyte, plasma or plasma-plateletfractions is desirable for the preparation of autologous concentratesfrom blood obtained from a patient during surgery. Each fraction can bemodified or returned to the blood donor. Useful plasma fractions, withour without platelets, have value as sealants when concentrated withoutprecipitation of fibrinogen, that is, when concentrated by removal ofwater therefrom in accordance with this invention. This invention hasparticular value for rapidly preparing autologous concentrated plasmafractions to help or speed healing, or as a hemostatic agent or tissuesealant.

Background of the Invention of U.S. Published Patent Application No.2004/0182795, by Randel Dorian and Richard Storrs, the entire contentsof which are hereby incorporated herein by reference: Blood may befractionated and the different fractions of the blood used for differentmedical needs. For instance, anemia (low erythrocyte levels) may betreated with infusions of erythrocytes. Thrombocytopenia (lowthrombocyte (platelet) levels) may be treated with infusions of plateletconcentrate.

Under the influence of gravity or centrifugal force, blood spontaneouslysediments into layers. At equilibrium the top, low-density layer is astraw-colored clear fluid called plasma. Plasma is a water solution ofsalts, metabolites, peptides, and many proteins ranging from small(insulin) to very large (complement components). Plasma per se haslimited use in medicine but may be further fractionated to yieldproteins used, for instance, to treat hemophilia (factor VIII) or as ahemostatic agent (fibrinogen).

Following sedimentation, the bottom, high-density layer is a deep redviscous fluid comprising anuclear red blood cells (erythrocytes)specialized for oxygen transport. The red color is imparted by a highconcentration of chelated iron or heme that is responsible for theerythrocytes high specific gravity. Packed erythrocytes, matched forblood type, are useful for treatment of anemia caused by, e.g.,bleeding. The relative volume of whole blood that consists oferythrocytes is called the hematocrit, and in normal human beings canrange from about 38% to about 54%.

Depending upon the time and speed of the centrifugation, an intermediatelayer can be formed which is the smallest, appearing as a thin whiteband on top the erythrocyte layer and below the plasma; it is called thebuffy coat. The buffy coat itself generally has two major components,nucleated leukocytes (white blood cells) and anuclear smaller bodiescalled platelets (thrombocytes).

Leukocytes confer immunity and contribute to debris scavenging.Platelets seal ruptures in the blood vessels to stop bleeding anddeliver growth and wound healing factors to the wound site. If thecentrifugation is of short duration, the platelets can remain suspendedin the plasma layer.

The sedimentation of the various blood cells and plasma is based on thedifferent specific gravity of the cells and the viscosity of the medium.This may be accelerated by centrifugation according approximately to theSvedberg equation:

V=((2/9)ω² R(d _(cells) −d _(plasma))r ²)/η_(t) where

-   V=sedimentation velocity, [00111] m=angular velocity of rotation,-   R=radial distance of the blood cells to the center of the rotor,-   d=specific gravity,-   r=radius of the blood cells, and-   η_(t)=viscosity of the medium at a temperature of t° C.

When sedimented to equilibrium, the component with the highest specificgravity (density) eventually sediments to the bottom, and the lightestrises to the top. The rate at which the components sediment is governedroughly by the Svedberg equation; the sedimentation rate is proportionalto the square of the size of the component. In other words, at firstlarger components such as white cells sediment much faster than smallercomponents such as platelets; but eventually the layering of componentsis dominated by density.

Soft Spin Centrifugation

When whole blood is centrifuged at a low speed (up to 1,000 g) for ashort time (two to four minutes), white cells sediment faster than redcells; and both sediment much faster than platelets (according to theSvedberg equation shown above). At higher speeds the same distributionis obtained in a shorter time. This produces layers of blood componentsthat are not cleanly separated and consist of (1) plasma containing themajority of the suspended platelets and a minor amount of white cellsand red cells, and (2) below that a thick layer of red cells mixed withthe majority of the white cells and some platelets. The method ofharvesting platelet-rich plasma (PRP) from whole blood is based on thisprinciple. The term “platelet-rich” is used for this component becausemost of the platelets in the whole blood are in the plasma followingslow centrifugation so the relative concentration of platelets in theplasma has increased.

Centrifugal sedimentation that takes the fractionation only as far asseparation into packed erythrocytes and PRP is called a “soft spin.”“Soft spin” is used herein to describe centrifugation conditions underwhich erythrocytes are sedimented but platelets remain in suspension.“Hard spin” is used herein to describe centrifugation conditions underwhich platelets sediment in a layer immediately above the layer oferythrocytes.

Two Spin Platelet Separation

Following a soft spin, the PRP can removed to a separate container fromthe erythrocyte layer, and in a second centrifugation step, the PRP maybe fractioned into platelet-poor plasma (PPP) and platelet concentrate(PC). In the second spin the platelets are usually centrifuged to apellet to be re-suspended later in a small amount of plasma or otheradditive solution

In the most common method for PRP preparation, the centrifugation ofwhole blood for 2 to 4 min at 1,000 g to 2,500 g results in PRPcontaining the majority of the platelets. After the centrifugation of aunit (450 ml) of whole blood in a 3-bag system the PRP is transferred toan empty satellite bag and next given a hard spin to sediment theplatelets and yield substantially cell-free plasma. This is termed“two-spin” platelet separation.

To recover the platelets following two-spin separation, most of theplatelet poor plasma (PPP) is removed except for about 50 ml and thepellet of platelets is loosened and mixed with this supernatant.Optionally one can remove about all plasma and reconstitute withadditive solution. To allow aggregated platelets to recover the mixtureis given a rest of one to two hours before platelets are againresuspended and then stored on an agitator.

It is believed that two-spin centrifugation can damage the platelets bysedimenting the platelets against a solid, non-physiological surface.The packing onto such a surface induces partial activation and may causephysiological damage, producing “distressed” platelets which partiallydisintegrate upon resuspension.

Hard Spin Centrifugation

If the centrifugation is continued at a low speed the white cells willsediment on top of the red cells whereas the platelets will remainsuspended in the plasma. Only after extended low speed centrifugationwill the platelets also sediment on top of the red cells.

Experiments with a blood processor have shown that centrifugation at ahigh speed (2,000 g-3,000 g) produces a similar pattern of cellseparation in a shorter time. Initially the cells separate according tosize, i.e., white cells sediment faster than red cells and plateletsremain in the plasma. Soon the red cells get ‘packed’ on each othersqueezing out plasma and white cells. Because of their lower density,white cells and platelets are pushed upwards to the interface of redcells and plasma whereas the platelets in the upper plasma layer willsediment on top of this interface, provided the centrifugal force issufficiently high and sedimentation time is sufficiently long. Plasma,platelets, white cells and red cells will finally be layered accordingto their density. Platelets sedimented atop a layer of red cells areless activated than those isolated by the “two spin” technique.

Leukoreduction

The PC's resulting from both two spin processing and apheresis methodscontain donor leukocytes. In apheresis, centrifugal blood processing isa growing field, per-processing bowl and to pick up variouscentrifugally permitting the continuous removal of blood from a patient,separated components of the material during centrifugation thenadministration of the depleted blood back to the patient (U.S. Pat. No.4,389,206, the entire contents of which are hereby incorporated hereinby reference). The white cells negatively affect platelet storage andmay induce adverse effects after transfusion due to cytokine formation.Removal of leukocytes (leukoreduction) from PRP and PC is importantbecause non-self leukocytes (allogeneic leukocytes) and the cytokinesthey produce can cause a violent reaction by the recipient's leukocytes.In 1999 the FDA Blood Product Advisory Committee recommended routineleukoreduction of all non-leukocytes components in the US (Holme 2000).Therefore, much of the prior art focuses on leukoreduction of plateletconcentrates because non-autologous leukocytes excite deleterious immunereactions. Since the process of this invention provides a convenient wayto quickly harvest autologous platelets from the patient's blood, immunereactions are not a risk, and the presence of leukocytes is of little orno concern.

Plasma concentrates and their utility in hemostasis and wound healinghave been described in U.S. Pat. No. 5,585,007. Plasma concentrates canbe made in a two-step method, first separating of plasma from themajority of erythrocytes and then concentrating the plasma by removingwater. The plasma can be separated from the erythrocytes bycentrifugation. The water can be removed from the plasma using asemipermeable membrane or by contact with a desiccated hydrogel bead.The membrane and hydrogel bead pores allow passage of water, salts andother low molecular weight components while blocking passage of cells,platelets (thrombocytes), cell fragments and larger molecules such asfibrinogen. The passage of water and low molecular weight componentsthrough the membrane or into the bead concentrates the plasma, the cellsand high molecular weight components contained therein. The dry hydrogelbeads can be dextranomer or polyacrylamide.

Recent publications report that platelet preparations enhance thehealing rate of hard and soft tissue defects. Activated cytokineproteins, released from activated platelets, signal the migration,proliferation and activation of monocyte cells. Monocyte cells sense agradient of cytokines and migrate towards the source.

Fibers of polymerized fibrin form pathways by which monocyte cellstranslocate into the wound. Translocation is enhanced by tension onthese fibers imparted by the action of platelet microtubules during clotretraction. Therefore, in situ polymerization of platelet-containingfibrinogen solutions provides an enhanced setting for wound healing.Platelet-plasma concentrates provide enhanced signals and pathways forwound healing cell migration.

Platelets have a limited half-time in vivo, and platelet activitydeclines rapidly ex vivo. An optimal wound healing compound thereforewould contain freshly isolated platelets. To minimize risk of diseasetransmission and maximize beneficial patient response to plateletactivity the platelet/plasma concentrate would preferably be preparedfrom the patient's own blood, i.e. autologously. The amount of bloodwithdrawn from the patient should be as small as possible to minimizemorbidity caused by blood loss.

The invention of U.S. Patent Application Publication No. 2004/0182795 byRandel Dorian and Richard Storrs provides methods and apparatus forrapidly separating patient plasma from whole blood, contacting saidplasma with dry hydrogel beads, concentrating said plasma, andseparating the resulting plasma concentrate from the beads forapplication to patient wounds.

Dorian's invention relates to a device for preparing plasma concentratefrom plasma containing cells (plasma cell mixture) comprising acentrifugal separation chamber having a plasma-cell mixture inlet portand a centrifugal separation chamber outlet port. The concentratingchamber has an inlet port and a concentrate outlet, the inlet portcommunicating with the centrifugal separation chamber outlet port, theconcentrating chamber containing hydrogel beads and at least one inertagitator. The device also includes a concentrate chamber having an inletcommunicating with the concentrate outlet through a filter, theconcentrate chamber having a plasma concentrate outlet port. A plungercan be positioned in the concentrating chamber. The concentratingchamber has an inner concentrating chamber wall, the plunger having anouter edge surface conforming to a surface of the inner concentratingchamber wall; and the hydrogel beads and agitator can be positioned inthe concentrating chamber between the plunger and the filter. The outeredge surface of the piston can form a sealing engagement with thesurface of the inner concentrating chamber wall.

In one embodiment, the centrifugal separation chamber has anerythrocyte-plasma interface level, and the centrifugal chamber outletport is positioned above the erythrocyte-plasma interface level. Theconcentrating chamber can have an unconcentrated plasma-air interfacelevel, the centrifugal separation chamber outlet port and theconcentrating chamber inlet port form an open passageway for flow ofplasma, and the concentrating chamber inlet port is positioned at alevel above said plasma-air interface level. Alternatively, thecentrifugal separation chamber can have a one-way valve permitting flowof plasma from the centrifugal separation chamber into the concentratingchamber. In these embodiments, the agitator can be a dense object suchas a smooth ball which can be a stainless steel. The filter can be aporous frit.

The term “plasma concentrate” is defined to include both plasmaconcentrate with platelets and plasma concentrate without platelets.

A method of Dorian's invention for producing plasma concentrate fromplasma containing erythrocytes and platelets can comprise the steps of(a) centrifugally separating a plasma-cell mixture to form anerythrocyte-rich layer and a plasma layer; (b) moving the plasma fromthe plasma layer into a concentrating chamber containing hydrogel beadsand an agitator to form a hydrogel bead-plasma mixture; (c) causing theagitator to stir the hydrogel bead-plasma mixture, minimizing gelpolarization and facilitating absorption of water by the beads from theplasma, until a hydrogel bead-plasma concentrate is formed; and (d)separating plasma concentrate from the hydrogel beads from the hydrogelbead-plasma concentrate by passing the plasma concentrate through afilter. The hydrogel beads can have the effective absorption capacity toremove at least 10 percent of the water from the plasma, at least 25percent of the water from the plasma, or at least 50 percent of thewater from the plasma. The plasma containing erythrocytes and plateletscan be whole blood.

Dorian's invention can be a method for producing plasma concentrate witha plasma concentrating device comprising a centrifugal separationchamber having a plasma-cell mixture inlet port and an centrifugalseparation chamber outlet port; a concentrating chamber having a inletport and a concentrate outlet, the inlet port communicating with thecentrifugal separation chamber outlet port, the concentrating chambercontaining hydrogel beads and at least one inert agitator; and aconcentrate chamber having an inlet communicating with the concentratingoutlet through a filter, the concentrate chamber having a plasmaconcentrate outlet port. With this device, the method can comprise (a)centrifuging a plasma-cell mixture in the centrifugal separation chamberto form an erythrocyte-rich layer and a plasma layer; (b) moving theplasma from the plasma layer through the separation chamber outlet portthrough the inlet port of the concentrating chamber to form a hydrogelbead-plasma mixture; (c) causing the agitator to stir the hydrogelbead-plasma mixture, minimizing gel polarization and facilitatingabsorption of water by the beads from the plasma, until a hydrogelbead-plasma concentrate is formed; and (d) separating plasma concentratefrom the hydrogel beads from the hydrogel bead-plasma concentrate bypassing the plasma concentrate through the filter and the concentratingchamber outlet port.

In Dorian's method, a plunger can be positioned in the concentratingchamber, the hydrogel beads and agitator are positioned in theconcentrating chamber between the plunger and the filter, and theconcentrating chamber has an inner concentrating chamber wall, theplunger having an outer edge surface conforming to a surface of theinner concentrating chamber wall. With this variation of the device, themethod can comprise (a) centrifuging a plasma cell mixture in thecentrifugal separation chamber to form an erythrocyte-rich layer and aplasma layer; (b) moving plasma from the plasma layer through theinlet/outlet port and the filter by axial movement of the plunger in theproximal direction away from the filter; (c) moving the plasmaconcentrating device in alternative distal and proximal directions alongthe central axis of the concentrating chamber to stir the hydrogelbead-plasma mixture, minimizing gel polarization and facilitatingabsorption of water by the beads from the plasma, until a hydrogelbead-plasma concentrate is formed; and (d) separating plasma concentratefrom hydrogel beads by moving the plasma concentrate through the filter.In step (d) the plasma concentrate can be moved through the filter andinto the concentrate outlet by moving the plunger in the distaldirection toward the filter. Other means of moving the plasmaconcentrate through the filter are within the intended scope of thisinvention, such as movement by centrifugal force or suction, forexample.

In U.S. Pat. No. 7,553,413, dated Jun. 30, 2009 entitled “PLASMACONCENTRATOR DEVICE,” the inventors Randel Dorian, Michael D. Leach andRichard Wood Storrs, the entire contents of which are herebyincorporated herein by reference, disclose a plasma concentrator of thisinvention having a concentrator chamber, concentrator gel beads, afilter, and an agitator. The agitator has agitator blades extendingoutwardly from the lower end. The agitator end is positioned in theconcentrator chamber and supported for rotation about its central axisand for reciprocal movement along its central axis. The concentrator hasa top with an upper opening through which the upper end of the actuatorstem extends, and a lower opening in which the filter is positioned. Theconcentrator chamber can have a cylindrical inner wall, and the agitatorblades can have an outer edge in close proximity to the inner wall withthe space between the outer edge and the inner wall being less than thediameter of the gel beads. The filter is selected to block effectiveflow of plasma therethrough under ambient gravity conditions and permitplasma and plasma concentrate flow therethrough under centrifugal forcesof the separation gravity. The method concentrates plasma by removingwater without significantly denaturing the fibrinogen in the plasma. Theplasma is introduced into a concentration chamber containing a pluralityof dehydrated concentrator gel beads and an agitator. Then water isremoved from the plasma while stirring the beads to reduce plasmapolarization and breaking up clumps of beads that form during theagitation. Then centrifugal force can be applied to the concentratedplasma in an amount sufficient to separate a substantial portion of theplasma concentrate from the beads.

A major improvement in making plasma concentrate from whole blood foruse in wound healing and as a tissue sealant is described in U.S. Pat.No. 5,585,007; this patent is hereby incorporated herein by reference inits entirety. This device, designed for placement in a medicallaboratory or surgical amphitheater, used a disposable cartridge forpreparing tissue sealant. The device was particularly applicable forstat preparations of autologous tissue sealants. Preparation in theoperating room of 5 ml of sealant from 50 ml of patient blood requiredless than 15 minutes and only one simple operator step. There was norisk of tracking error because processing can be done in the operatingroom. Chemicals added could be limited to anticoagulant (e.g., citrate)and calcium chloride. The disposable cartridge could fit in the palm ofthe hand and was hermetically sealed to eliminate possible exposure topatient blood and ensure sterility. Adhesive and tensile strengths ofthe product were comparable or superior to pooled blood fibrin sealantsmade with precipitation methods. Use of antifibrinolytic agents (such asaprotinin) was not necessary because the tissue sealant contained highconcentrations of natural inhibitors of fibrinolysis from the patient'sblood. This new tissue sealant also optionally contained patientplatelets and additional factors that promote wound healing, healingfactors that are not present in commercially available fibrin sealants.

This device used a new sterile disposable cartridge with the separationchambers for each run. Since the device was designed to be used in anormal medical setting with ample power, the permanent components,designed for long-term durability, safety and reliability, wererelatively heavy, using conventional centrifuge motors and accessories.

Small, self-contained centrifugal devices for obtaining plateletconcentrates from blood are described in application Ser. No. 10/394,828filed Mar. 21, 2003, the entire contents of which are herebyincorporated herein by reference. This device separates blood intoerythrocyte, plasma and platelet layers and selectively removes theplatelet layer as a platelet concentrate, that is, platelets suspendedin plasma. The plasma fraction, being in an unconcentrated form, is noteffective as a hemostat or tissue.

In a patent application entitled “Buoy Suspension Fractionation System”with the application Ser. No. 12/101,586 (Publication No. 2009/0014391A1), filed on Apr. 11, 2008, the entire contents of which are herebyincorporated herein by reference, Leach discloses a separator that usescentrifugation to fractionate a suspension such as blood comprises aseparation container and a buoy. The buoy is carried in the separationcontainer and has a tuned density that is configured to reach anequilibrium position in a suspension. The guide surface is carried onthe buoy upper surface and is inclined to an accumulation position neara buoy perimeter. The buoy suspension fractionation system can be usedin a method of isolating a fraction from a suspension, and in a methodfor re-suspending particulates for withdrawal.

In patent application entitled “Apparatus and method for separating andisolating components of a biological fluid” having application Ser. No.12/315,722 (Publication No. 2010/0140182 A1) and a filing date of Dec.4, 2008, the entire contents of which are hereby incorporated herein byreference, Chapman et al. discloses that it is known to separatebiological fluids, such as aspirated bone marrow or peripheral blood,into their component parts, fractions, phases, or constituent layers bycentrifugation. It is also known to provide mechanical devices comprisedof a tube which houses a solid separator which, when actuated bycentrifugal force, allows biological fluid to flow through or around thepiston based on differing relative densities thereby separating thebiological fluid into a one or more component parts above and one ormore component parts below the solid separator. For example, when thebiological fluid within the tube is blood, the centrifugation processresults in a high density layer of red blood cells below the solidseparator, a low density layer of plasma above the solid separator, anda buffy coat layer which defines an intermediate density layer or thirdfraction above the solid separator and below the low density layer ofplasma.

One of the earliest solid separators was disclosed in U.S. Pat. No.3,508,653, issued Apr. 28, 1970 to Coleman, the entire contents of whichare hereby incorporated herein by reference. That device was a rubber orother elastomeric cylinder. A major problem with that device was theinability to maintain a seal because it is costly to maintain theprecise inner diameter of the test tube when mass produced. A subsequentsolid separator development is disclosed in U.S. Pat. No. 3,814,248,issued Jun. 4, 1974 to Lawhead, the entire contents of which are herebyincorporated herein by reference. Next, U.S. Pat. No. 3,779,383, issuedDec. 18, 1973 to Ayres, the entire contents of which are herebyincorporated herein by reference, disclosed a device in which the bloodintroduction end of the tube is opposite to the movable separator end ofthe tube, and abutting an impenetrable rubber closure. Following Ayres,U.S. Pat. No. 3,931,018, issued Jan. 6, 1976 to North, Jr., the entirecontents of which are hereby incorporated herein by reference, discloseda solid separator for use in separation of blood serum and blood plasmausing centrifugal force that must be inserted into the blood collectiontube after blood collection.

In a patent to Levine, et al. (U.S. Pat. No. 4,159,896, issued Jul. 3,1979), the entire contents of which are hereby incorporated herein byreference, a centrifugally motivated solid separator device is disclosedin which a cylindrical float is disposed inside of a tube, which floathas an accurately controlled outside diameter so as to fit snugly in thetube bore under static conditions. When used in harvesting blood cellsthe float is formed with an axial through bore which receives andexpands the white cell and platelet layers in the blood sample aftercentrifugation thereof. The disclosed float was made from a plasticmaterial having a specific gravity that causes it to float in the packedred cells after centrifugation of the blood sample in the tube.

In another patent to Levine, et al, (U.S. Pat. No. 5,393,674, issuedFeb. 28, 1995), the entire contents of which are hereby incorporatedherein by reference, a clear plastic tube large enough to process 1 mlof blood and equipped with a cylindrical float and filled with an inertgas at low pressure is disclosed. The float contains a through bore, andprior to centrifugation, is held fixably at an initial location by tightcontact between the exterior of the float and the interior wall of thetube. Unlike the inventions of Coleman, which contain pistons (or buoys)with no through bore, the Levine float relocates, under centrifugation,to a new position determined by its density relative to the density ofthe blood fractions as a result of the shrinkage of its diameter due tothe longitudinal elongation (and subsequent lateral narrowing) of thefloat body that results from the substantial gravity gradient thatoccurs from the top to the bottom of the float. This substantial G forcegradient (several thousand Gs) causes the float to elongate and narrowjust as a rubber tube elongates and narrows when pulled from both ends.This space between the exterior of the float and the interior of thetube that develops during centrifugation provides the freedom ofmovement of the float consequent with the motion of the blood componentsto their new location determined by their density relative to the float.Levine does not posit, but it is assumed that some of the redistributingblood components also travel through the bore during centrifugation butsince the top and bottom of the through bore are not closed, any cellsand platelets that wind up there following centrifugation are easilyinfiltrated by the red cells and plasma during normal postcentrifugation handling. Designed predominately as a diagnostic toolthat proceeds through the visual examination of the cells that at leasttemporarily occupy the through bore right after centrifugation, Levinealso discloses the possibility of extracting these cells with a syringeneedle for additional diagnostic examination. This method of extractionnecessarily is inefficient as a means of cell recovery as the intrudingneedle necessarily relocates the target cells above and below thethrough bore as it is inserted.

Hence, these known mechanical devices are generally capable ofseparating biological fluids into component parts or fractions; however,these devices are not very precise thereby resulting in inefficientseparation of the biological fluid into component parts or fractionsbecause of the substantial commingling of the separated fractions.Additionally, these known mechanical devices fail to provide a simple orefficient method to extract a fraction other than the top fraction ofthe sample leading to low recoveries, especially of the clinicallyimportant buffy coat fraction.

It is also known to provide more complicated mechanical devices in anattempt to alleviate the above known problems. For example, the patentto Leach, et al. (U.S. Pat. No. 7,374,678, issued May 20, 2008), theentire contents of which are hereby incorporated herein by reference, ina first embodiment, discloses a device for separating a sample, such asblood, into a plurality of fractions. The device is comprised of aplunger (or second piston) which, prior to centrifugation, is retainedproximate a top end of a closed ended distortable tube duringcentrifugation and a first piston (or buoy) which is tightly fitted nearthe bottom of the closed ended distortable tube such that undercentrifugation with a sample of blood, the tube wall longitudinallycompresses and bows outward thereby allowing the buoy to move in adirection of the top of the tube lifted by a layer of red blood cells ofhigher density than the piston that has flowed downward between the buoyand the interior of the tube wall. After centrifugation, the tube wallreturns to its original dimension and traps this first piston at a newlocation coinciding with the interface position of a top plasma fractionand a bottom red blood fraction of the separated sample. On or near acollection face of this first piston (or buoy) is a third fraction whichincludes “a small, yet concentrated, amount of red blood cells, whiteblood cells, platelets, and a substantial portion of a buffy coat of theblood sample.” The device then employs a plunger (or second piston)which is manually pushed down into the tube from a location proximatethe top end of the tube. The plunger (or second piston) includes a valvewhich allows the plasma to pass through the plunger to while the plungeris lowered to a predetermined depth above the first piston set by adepth gauge which locates the plunger a distance away from thecollection face of the piston thereby defining a third fraction betweena bottom face of the plunger (or second piston) and the collection faceof the first piston. The extraction of the third fraction isaccomplished via a vacuum created on a tube extending between acollection valve disposed in the top of the tube and a bore extendingfrom the top of the plunger and the bottom of the plunger.

Accordingly, this device relies on the imprecise longitudinalcompression and decompression of the tube wall in order to control theflow path between fractions and fails to contain the separated fractionsuntil after centrifugation stops and the tube wall returns to itsoriginal dimensions. Furthermore, the extraction of the third fractionrequires infiltration of the top plasma fraction. Hence, this recentlypatented device still fails to alleviate the problem of inefficientseparation of the biological fluid into component parts or fractions andthe commingling of the separated fractions.

In another embodiment, Leach, et al. discloses that the plunger (orsecond piston) is rigidly or slideably fitted with the first piston orbuoy such that the pair is tightly fitted within the closed endeddistortable tube wherein under centrifugation with a sample such ofblood, the tube wall bows outward thereby allowing the pair to move in adirection of the top of the tube while lifted by a high density layer ofred blood cells flowing downward between the pair and the interior ofthe tube wall. After centrifugation, the tube wall returns to itsoriginal dimension which grips the periphery of the first piston at aninterface position of a plasma fraction and a red blood fraction of theseparated sample. On or near a collection face of this first piston is“a small, yet concentrated, amount of red blood cells, white bloodcells, platelets, and a substantial portion of a buffy coat of the bloodsample.” The extraction of the intermediate (buffy coat) or thirdfraction is accomplished “by interconnecting a cannula or bored tubewith the connection portion of the buoy cylinder” and connecting anextraction syringe to the cannula for creating a vacuum to draw theintermediate or third fraction from the space between the first andsecond pistons. This embodiment describes only one centrifugation spin,and fails to alleviate the problem of inefficient separation of thebiological fluid into component parts or fractions and the comminglingof the separated fractions. Furthermore, the extraction of a fractionother than the top fraction still requires the infiltration of at leastone other fraction than the desired fraction to be extracted. Moreover,the device relies on the imprecise longitudinal compression anddecompression of the tube wall in order to control the flow path betweenfractions and fails to contain the separated fractions untilcentrifugation stops and decompression of the tube wall is concluded.

Another problem associated with both embodiments of Leach, et al. isthat the collection face, trough, or sump of the buoy must be shallow tobe at a desired density level of the target buffy coat fraction and topreclude even further accumulation of reds cells with the target whitecells and platelets to be extracted. Thus, this shallow trough resultsin having the target white blood cells and platelets, come to rest onthe entire large surface area of the first piston on which the whiteblood cells and platelets tend to stick, which reduces the efficiency ofthe final collection step. A further problem associated with bothembodiments of Leach, et al. is the time consuming and laborious processof fitting and interconnecting multiple parts to the device in order toperform the extraction process.

In general, current processes for separating and extracting fractionsout of biological fluids require multiple steps that are both laboriousand time consuming and that result in poor recoveries of the targetwhite cells and platelets. Hence, it would be desirable to provide asimplified and more effective process so less time, labor, and trainingis required to do the procedure and fewer white cells and platelets arelost thereby providing a positive economic impact. A simplified processwould also allow it to be performed in an intra-operative setting by anoperating room nurse, rather than a remote laboratory setting by atechnician so that a patient can be more rapidly treated and thepossibility of mixing up samples can be essentially eliminated. Processsimplification also has a direct correlation to process reproducibilitythat is also a problem with the known prior art.

Hence, the known prior art is problematic in a number of areas whichinclude a deficiency in the recovery efficiency of cells of interest(target cells), in the selectivity of separation for reducingcontamination or non-target cells from the target cell population, andin the multiple step, laborious, and time consuming extraction process.A summary of the invention of Chapman disclosed in application Ser. No.12/315,722 is a device for separating and isolating components of abiological fluid comprising a container for containing the fluid to beprocessed, a tube cap assembly for closing the container while providingfilling and extraction communication therewith, a float assemblydisposed within the container for funneling and controlling biologicalfluid flow into an inverted domed shaped isolation chamber within thefloat and controlling the biological fluid flow out of the isolationchamber for effecting an encapsulation or a sealed isolation of at leastone component or fraction of the biological fluid flow within theisolation chamber during a centrifugation process. The device furthercomprising a flexible tube for connecting an extraction passagewaydisposed within the float assembly and an extraction valve of the tubecap assembly for allowing extraction of at least the one component orfraction encapsulated or isolated within the chamber.

The Goddard et. al in U.S. Patent Application Publication No.2007/0259330 A1 published on Nov. 8, 2007, the entire contents areincorporated herein by reference, describe an invention that relates tothe field of cell separation, and more specifically to a method ofseparating mononuclear cells from blood. The Goddard invention alsoencompasses a separation media which is used in the present method, acontainer filled with such media and a kit useful in cell separation.

U.S. Pat. No. 5,474,687 (Activated Cell Therapy), the entire contentsare incorporated herein by reference, relates to the enrichment of CD34+cells. More specifically, a method is disclosed, which compriseslayering a cell mixture containing CD34+ cells into a centrifuge tube,said density gradient solution having an osmolality of 280±10 mOsm/kgH2O and a specific density within 0.0005 g/ml of the specific density ofsaid CD34+ cells; centrifuging said tube at a gravitational forcesufficient to pellet cells having specific densities greater than thespecific density of the density gradient material in said tube; andcollecting from the upper portion of said tube an enriched population ofCD34+ cells. The tube used in the method comprises an annular memberdisposed in said tube and defining an opening there through, whichopening has an area less than the area of a cross section of the tube.

In one embodiment, the method further comprises incubating said cellmixture with a cell type-specific binding agent linked to carrierparticles prior to centrifugation, said particles having a specificdensity that is at least 0.001 g/ml greater than the specific density ofsaid density gradient solution. This binding agent may bind to non-CD34+cells, and may e.g. be an antibody directed to the CD45 antigen. Thedensity gradient solution may e.g. be selected from the group consistingof Percoll™, Ficoll™, Ficoll-Hypaque™, albumin, sucrose and dextran. Asappears from the above, there is still a need in this field of novelpurification protocols which allow efficient purification of viablemononuclear cells from blood in yields useful for clinical applications.

The invention of Vlasselaer disclosed in U.S. Pat. No. 5,474,687 datedDec. 12, 1995, the entire contents are incorporated herein by reference,relates to methods of enriching hematopoietic progenitor cells from bodyfluids. In particular, it relates to the use of a cell-trapcentrifugation tube containing a gradient solution adjusted to aspecific density to enrich for CD34+ cells from apheresed blood. Thetube allows the desired cell population to be collected by decantationafter centrifugation to minimize cell loss and maximize efficiency. Inaddition, the method can be further simplified by density-adjusted cellsorting which uses cell type-specific binding agents such as antibodiesand lectins is linked to carrier particles to impart a different densityto undesired cell populations allowing the progenitor cells to beseparated during centrifugation in a more convenient manner. The rapidprogenitor cell enrichment method described herein has a wide range ofapplications, including but not limited to, donor cell preparation forbone marrow transplantation without the use of invasive procedures suchas bone marrow aspiration.

The invention of Inbar et al. disclosed in U.S. Pat. No. 5,314,074 datedMay 24, 1994 entitled “Method and Means for Density GradientCentrifugation,” the entire contents are incorporated herein byreference, discloses a method and means for density gradientcentrifugation.

U.S. Pat. No. 4,824,560, the entire contents are incorporated herein byreference, discloses method and means for centrifugation by which atubular vessel is used with at least two compartments in a rowcommunicating with one another via a narrow, essentially capillaryopening. For operation, the working fluid is charged into the lowercompartment and the liquid to be centrifuged into the upper one with noneed for any special precautions to avoid mixing prior tocentrifugation. While this method has some significant advantage overthe above-described purely manual methods, it has the drawback that therather narrow passage between the compartments provides some resistanceeven during centrifugation which may prolong the operation. Moreover,the method requires specially devised centrifugation vessels whichrenders it relatively costly. Furthermore, since in accordance with thatmethod the entire lowermost compartment must be filled with workingfluid it is not possible to vary the amount of working fluid in a givencentrifugation vessel.

In 2008, C. Nilsson, et al. published a paper entitled “Optimal BloodMononuclear Cell Isolation Procedures for Gamma Interferon Enzyme-LinkedImmunospot Testing of Healthy Swedish and Tanzanian Subjects” in ClinVaccine Immunol. 15(4): 585-589, the entire contents are incorporatedherein by reference, in which they compared different existing methodsof density gradient separation of peripheral blood.

It is known in the prior art to digest tissues to release cells. Suchcell suspensions can be made from surgically removed tumors or fromnormal tissue such as adipose. Gimble et al published a reviewmanuscript in Circulation Research 100(9) 1249-60 entitled“Adipose-derived stem cells for regenerative medicine” for which theentire contents are incorporated herein by reference, which reviews theknown art of cell isolation and mechanical devices for adipose tissueprocessing. References cited refer to article references found in thepublication of Gimble.

The initial methods to isolate cells from adipose tissue were pioneeredby Rodbell and Rodbell and Jones in the 1960s. They minced rat fat pads,washed extensively to remove contaminating hematopoietic cells,incubated the tissue fragments with collagenase, and centrifuged thedigest, thereby separating the floating population of mature adipocytesfrom the pelleted stromal vascular fraction (SVF). The SVF consisted ofa heterogeneous cell population, including circulating blood cells,fibroblasts, pericytes, and endothelial cells as well as “preadipocytes”or adipocyte progenitors. The final isolation step selected for theplastic adherent population within the SVF cells, which enriched for the“preadipocytes.”

Subsequently, this procedure has been modified for the isolation ofcells from human adipose tissue specimens. Initially, fragments of humantissue were minced by hand; however, with the development of liposuctionsurgery, this procedure has been simplified. During tumescentliposuction, plastic surgeons infuse the subcutaneous tissues with asaline solution containing anesthetic and/or epinephrine via a cannulaand then remove both the liquid and tissue under suction. The proceduregenerates finely minced tissue fragments, the size of which depends onthe dimensions of the cannula. Independent studies have determined thatliposuction aspiration alone does not significantly alter the viabilityof isolated SVF cells. Indeed, adherent stromal cells withcharacteristics of adipocyte progenitors can be found directly withinthe liposuction aspiration fluid, as well as in SVF derived from thetissue fragment digests. However, when ultrasound-assisted liposuctionis performed, the number of cells recovered from tissue digests isreduced, as is their proliferative capacity. The recovery of ASCs can beimproved further by manipulating the centrifugation speed. Investigatorshave achieved optimal cell recovery using a centrifugation speed of 1200g based on the subsequent formation of a human-derived adipose tissuedepot following implantation in an immunodeficient murine model.

The cell isolation process requires the manipulation of large volumes oflipid-laden cells, presenting potential risks to equipment andpersonnel. To facilitate the process, several groups have fabricateddevices to automate the cell isolation. One approach uses a “bag withina bag.” The suctioned aspirate flows through a central bag thatautomatically sieves the tissue while draining away the aspirationfluid. Subsequently, the trapped tissue can be washed and furthermanipulated. Others have developed a closed, rotating, controlledtemperature incubator capable of collagenase digesting and separating upto one liter of tissue at a time. These prototypes may one day lead tocommercially available manufactured devices for large scale, automatedadipose tissue manipulation and cell isolation suitable for clinicalapplications.

Collas discloses a protocol for separation of the stromal vascularfraction from adipose consists of the following steps:

Lipoaspirate Washing

It is necessary to wash the lipoaspirate extensively to remove themajority of the erythrocytes and leukocytes. The following proceduresshould be performed under aseptic conditions. Place a maximum of 300 mlof lipoaspirate into a used sterile medium bottle. Allow the adiposetissue to settle above the blood fraction. Remove the blood using asterile 25 ml pipette. Add an equivalent volume of HBSS with antibioticsand fungizone and firmly tighten the lid. Shake vigorously for 5-10seconds. Place the bottle on the bench and allow the adipose tissue tofloat above the HBSS. This will take 1-5 min depending on the sample.

Carefully remove the HBSS using a 50 ml pipette. Repeat the abovewashing procedure (steps 4 to 7) three times. Medium from the final washshould be clear. If it is still red, wash again by repeating steps 4.

Collagenase Digestion

Dispersion of adipose tissue is achieved by collagenase digestion.Collagenase has the advantage over other tissue digestive enzymes thatit can efficiently disperse adipose tissue while maintaining high cellviability. Make up collagenase solution just prior to digestion. Thefinal volume required is half that of the washed adipose tissue volume.Add powdered collagenase to HBSS at a final concentration of 0.2%. Wedissolve the required amount of collagenase into 40 ml of HBSS, thenfilter sterilize into the remaining working volume. Add antibiotics andfungizone. Add the washed adipose tissue to large cell culture flasks(100 ml per 162 cm2 flask). Add collagenase solution. Re-suspend theadipose tissue by shaking the flasks vigorously for 5-10 seconds.Incubate at 37° C. on a shaker for 1 to 2 h, manually shaking the flasksvigorously for 5-10 seconds every 15 min. During the digestion, prepareHistopaque gradients by dispensing 15 ml of Histopaque-1077 into 50 mltubes. Two gradients are required for each 100 ml of washed adiposetissue. The gradients must be equilibrated at room temperature beforeuse. Prepare 200 ml of washing medium consisting of HBSS containing 2%FBS, antibiotics and fungizone. On completion of the digestion period,the digested adipose tissue should have a “soup like” consistency. AddFBS to a final concentration of 10% to stop collagenase activity.

Separation of the Stromal-Vascular Fraction

After digestion, the ability of lipid-filled adipocytes to float is usedto separate them from the stromal vascular fraction (SVF). Dispense thecollagenase-digested tissue into 50 ml tubes. Avoid dispensingundigested tissue. Centrifuge at room temperature at 400×g for 10 min.After centrifugation, use a 50 ml pipette to aspirate the floatingadipocytes, lipids and the digestion medium. Leave the SVF pellet in thetube.

Separation of Stromal Stem Cells from the SVF

The SVF predominantly contains erythrocytes, leukocytes, endothelialcells and stromal stem cells. Erythrocytes are removed first, using thered blood cell lysis buffer.

Removal of erythrocytes. Re-suspend thoroughly each SVF pellet in 20 mlof cell lysis buffer at room temperature. Incubate at room temperaturefor 10 min. Centrifuge at 300×g for 10 min and aspirate the cell lysisbuffer.

Removal of cell clumps and remaining undigested tissue. It is essentialto obtain a cell suspension free from undigested tissue and cell clumps,to effectively separate stromal stem cells from other cell types usingantibody-conjugated magnetic beads. The strategies used to achieve thisare separation of gross undigested tissue using gravity, straining ofcells and gradient separation. Re-suspend SVF pellets thoroughly in 2 mlof washing medium using a 1 ml pipette. Pipet the cells up and downseveral times to reduce clumping. Pool the pellets into two 50 ml tubes.Allow undigested tissue clumps to settle by gravity for ˜1 min. Aspirateand pass the suspended cells through 100 μm cell strainers. Pass thefiltered cells through 40 μm cell strainers. Add extra washing buffer sothat the final volume is equivalent to that of the gradients (i.e., for4 gradients, the volume of cells in washing buffer should be 60 ml).

Ficoll Separation

Hold each tube containing Histopaque at a 45 degree angle and carefullyadd the cells by running the suspension along the inside wall of thetube at a flow rate of ˜1 ml per second. Careful layering of cells ontothe gradients is essential for successful cell separation. Centrifugegradients at exactly 400×g for 30 min. Carefully remove the medium (˜10ml) above the white band of cells found at the gradient interface anddiscard. Carefully remove the white band of cells (˜5 ml) by carefulaspiration and place into a new 50 ml tube. Add an equivalent volume ofwashing medium and centrifuge at 300×g for 10 min using a low brakesetting. Aspirate and re-suspend each pellet in 25 ml of washing medium.Centrifuge at 300×g for 10 min using a low brake setting.

Separation of stromal stem cells from endothelial cells and leukocytesby magnetic cell sorting.

Stromal stem cells are separated from remaining cells using magneticcell sorting. Unwanted endothelial (CD31+) and leukocytes (CD45+) aremagnetically labeled and eliminated from the cell suspension whenapplied to a column under a magnetic field. Magnetically labeled cellsare retained in the column, while unlabeled stem cells with a CD45−CD31−phenotype pass through the column and are collected. To this end, CD31+and CD45+ cells are labeled with FITC-conjugated anti-CD31 and anti-CD45antibodies. The stained cells are magnetically labeled by the additionof anti-FITC-conjugated magnetic micro-beads. This approach presents theadvantage that cell purity after separation can be assessed by flowcytometry or fluorescence microscopy. For the following steps, use coldbuffer and work on ice to reduce cell clumping. Re-suspend and pool thesedimented pellets in 10 ml of column buffer (PBS containing 2 mM EDTAand 0.5% BSA). Remove all remaining cell clumps by passing thesuspension through a 40 μm cell strainer. Perform a cell count. Transfercells to a 15 ml tube and centrifuge at 300×g for 10 min at 4° C. usinga low brake setting. Re-suspend the cell pellet in column buffer andlabel with anti-CD31 FITC-conjugated and anti-CD45 FITC-conjugatedantibodies according to the manufacturer's recommendations. Suspendcells in 100 μl of column buffer and add 10 μl of each antibody per 107cells. Mix well and incubate for 15 min in the dark at 4° C. (re-suspendthe cells after 7 min of incubation). Wash the cells to remove unboundantibody by adding 2 ml of column buffer per 107 cells. Centrifuge at300×g for 10 min at 4° C. using a low brake setting. Aspirate thesupernatant completely and re-suspend the cell pellet in 90 μl of columnbuffer per 107 cells. Add 10 μl of MACS anti-FITC magnetic micro-beadsper 107 cells. Mix well and incubate for 15 min at 4° C. (re-suspend thecells after 7 min of incubation). Wash the cells to remove unbound beadsby adding 2 ml of column buffer per 107 cells. Centrifuge at 300×g for10 min at 4° C. using a low brake setting. Aspirate the supernatantcompletely and re-suspend the cell pellet in 500 μl of column buffer.For magnetic cell separation, we use the MACS LD column specificallydesigned for the depletion of unwanted cells. Place a MACS LD columnonto the MidiMACS separation unit or onto a compatible unit. Prepare thecolumn by washing with 2 ml of column buffer. Apply the cell suspensionto the column and collect the flow-through unlabeled cells in a 15 mltube. Wash unlabeled cells through the column by twice adding 1 ml ofcolumn buffer. Collect the total effluent. Check for stem cell purity Ifhigher purity is required, centrifuge the collected cells at 300×g for10 min at 4° C. using a low brake setting and repeat steps 11-17.Perform a cell count. Centrifuge at 300×g for 10 min at 4° C. using alow brake setting. Use the cells as required or freeze the cellsaccording to standard protocols.

A patent was awarded to Fraser et al. in U.S. Pat. No. 7,390,484 on Jun.24, 2008 entitled “Self Contained Adipose Derived Stem Cell ProcessingUnit” for which the entire contents are incorporated herein byreference.

A paper was published by Conde-Green et al. entitled “Effects ofCentrifugation on Cell Composition and Viability of Aspirated AdiposeTissue Processed for Transplantation” in the Aesthetic Surgery Journalvol. 30 no. 2 249-255, 2010 for which the entire contents areincorporated herein by reference. The authors state centrifugation isone of the preferred methods of fat processing. Although it has beenpromoted for nearly three decades to separate adipose tissue componentsbefore grafting, there remain many controversies regarding the resultsobtained with centrifuged adipose tissue. In this paper, the authorsdemonstrate the effects of centrifugation on the cellular components ofaspirated fat.

To do the study, fat harvested from the lower abdomen of 10 femalepatients undergoing liposuction was divided in two equal parts, thenprocessed by decantation or centrifugation and sent to the laboratory.Each processed lipoaspirate was analyzed histologically afterhematoxylin and periodic acid-Schiff staining for the presence of intactadipocytes. It was then cultured and analyzed by multicolor flowcytometry for identification of adipose-derived mesenchymal stem cells.

The authors found the middle layer of the centrifuged lipoaspirate,which is used by many surgeons, showed a great majority of alteredadipocytes and very few mesenchymal stem cells in comparison with thedecanted sample, which maintained the integrity of the adipocytes andshowed a greater number of mesenchymal stem cells. The pellet observedas a fourth layer at the bottom of the centrifuged lipoaspirate showedthe greatest concentration of endothelial cells and mesenchymal stemcells, which play a crucial role in the angiogenic and adipogenic effectof the grafted tissue. It was concluded that if centrifuged lipoaspirateis used, the pellet (rich in adipose-derived mesenchymal stem cells) andthe middle layer should be employed to increase fat graft survival.

Xie et al. published a paper entitled “The effect of centrifugation onviability of fat grafts: an evaluation with the glucose transport test”in Journal of Plastic, Reconstructive & Aesthetic Surgery 63(3) 482-487,2010 for which the entire contents are incorporated herein by reference.

The authors state that an up-to-date, simple, but useful technique toevaluate the viability of fat grafts prior to transplant is lacking. Thepurpose of this study is to introduce the glucose transport test—a newmethod to evaluate the viability of fat grafts after they are subjectedto different centrifugal forces in vitro.

To conduct the their study, fat grafts were harvested from healthypatients who underwent liposuction for body contouring. The glucosetransport test was performed to evaluate the viability of fat graftsafter centrifugation with different forces (1000-4000 rpm). An MTT assaywas also performed with the same experimental protocol for comparison.Routine histological examination was done in all groups to examinepossible structural destruction after centrifugation.

When compared with the group not subjected to centrifugation, theglucose transport test showed a significant decrease in viability of fatgrafts in all of the other four groups (all p<0.001). There was a linearreduction of viability in fat grafts with the increase in centrifugalforce (all p<0.03). MTT assay showed similar findings on the viabilityof fat grafts in all five groups and correlated well with the glucosetransport test (r=0.9870). Histology showed significantly distorted andfractured adipocytes when the centrifugal force reached 4000 rpm. Theauthors conclude their study demonstrates the harmful effect on theviability of fat grafts with an increase in centrifugal force and, forthe first time, that the glucose transport test may be an effective andpotentially useful method to evaluate the viability of fat grafts in aclinical setting.

Anderson et al. was awarded U.S. Pat. No. 6,346,421 on Feb. 12, 2002entitled “Methods for Concentrating and Detecting Microorganisms UsingCentrifuge Tubes,” for which the entire contents are incorporated hereinby reference.

Graham et al were awarded U.S. Pat. No. 4,436,631 on Mar. 13, 1984entitled “Multiple Particle Washing System and Method of Use” for whichthe entire contents are incorporated herein by reference. Grahamdiscloses a particle washing system and method of use is wherein in apreferred embodiment the fluid containing the desired particles isplaced within an inner tube having near the bottom thereof an orificewith a diameter at least equal to that of the diameter of the particles,and wherein the inner tube is positioned within an outer tube having afluid with a density at least equal to that of the solution containingthe particles to be separated but less than that of the particles.

The application of centrifugal force to the particles directed towardthe bottom of the outer tube causes the particles to move through theorifice and through the outer solution contained within the outer tubeso that the particles are collected from the inner solution, washed bythe outer solution, and subsequently sedimented at the bottom of theouter tube. Graham's invention has the stated objective to permit therapid separation of particles from a solution in a “one step” operation.It is another objective that during separation of the particles from thesolution containing the particles, the particles are washed so as toremove any nonspecific serum coating and to dilute any solute drag. Itis yet another object that the original containing solution beseparately maintained from the resulting particle concentration topermit the removal of the original mother solution in order to reducecontamination. It is another object to permit the separation ofparticles having different densities and dispensing at least one of suchparticle types to the exclusion of the sucrose typically having amolecular weight of 5,000 or more. The serum albumin may be selectedfrom the group consisting of animal serum albumin and human serumalbumin. Serum albumin, to be compatible, cannot have human gammaglobulin or human complement.

The volumes of the washing solution and mother solution are chosen sothat the interface between these solutions is contained within the innerhollow tube. Upon the application of centrifugal force, the particlescontained within the mother solution, placed within the cavity formed bythe hollow inner cylinder, are forced to move through the mothersolution towards the bottom of the test tube in accordance with thesedimentation coefficients or Svedberg Units characterizing theparticles. Since the hollow interior cylinder is merely resting upon thebottom of the outer test tube, the washing solution is capable ofpenetrating into and out of the inner hollow cylinder and isconsequently, partially displaced.

It is still another objective of the present invention that theseobjectives be accomplished in a simple system capable of economicalproduction and employable within simple, inexpensive centrifugescommonly available. It is still yet another objective that the apparatusand methodology of the present invention be capable of replacingexpensive automated cell washers presently available. It is a furtherobjective of the present invention to not only provide methodologywhereby the objectives may be accomplished but also devices capable ofmeeting the desired objectives.

Rimm et al were awarded U.S. Pat. No. 6,197,523 on Mar. 6, 2001 entitled“Method for the Detection, Identification, Enumeration, and Confirmationof Circulating Cancer and/or Hematologic Progenitor Cells in WholeBlood” for which the entire contents are incorporated herein byreference. Rimm's method for analyzing blood enables one to isolate,detect, enumerate and confirm under magnification the presence orabsence of target cancer cells and/or hematologic progenitor cells whichare known to circulate in blood. The analysis is performed in a sampleof centrifuged anti-coagulated whole blood. The analysis involves bothmorphometric and epitopic examination of the blood sample while theblood sample is disposed in a centrifuged blood sampling tube.

The epitopic analysis of the presence or absence of cancer cells relieson the detection of epitopes which are known to present only on cancercells; and the epitopic analysis of the presence or absence ofhematologic progenitor cells relies on the detection of epitopes whichare known to present only on hematologic progenitor cells. The targetedepitopes on the target cell types are epitopes which are also known tobe absent on normal circulating blood cells; and the target cancer cellepitopes are epitopes which are known to be absent on target hematologicprogenitor cells. Fluorophors with distinct emissions are coupled withantibodies which are directed against the targeted epitopes.

The morphometric analysis is performed by staining the cells in theblood sample with an intracellular stain such as acridine orange whichhighlights the intracellular cell structure. Both the morphometric andepitopic analyses are preferably performed at or near the platelet layerof the expanded buffy coat in the centrifuged blood sample. Themorphometric analysis and/or the epitopic analysis may be performedunder magnification both visually and/or photometrically.

Rimm's invention relates to a method and assembly for the detection,identification, enumeration and confirmation of circulating cancerand/or hematologic progenitor cells in an anti-coagulated whole bloodsample which is contained in a transparent sampling tube assembly. Thedetection, identification, enumeration and confirmation steps can all beperformed in situ in the sampling tube assembly. More particularly, themethod of this invention involves the centrifugal density-basedseparation of the contents of the blood sample in a manner which willensure that any circulating cancer and/or hematologic progenitor cellsin the blood sample are physically displaced by their density into apredetermined axial location in the blood sample and in the samplingtube assembly, and also into a restricted optical plane in the samplingtube assembly which is adjacent to the wall of the sampling tube, andfinally into a very well defined zone of that optical plane.

Babson was awarded U.S. Pat. No. 4,639,242 on Jan. 27, 1987 entitled“Vessel and Procedure for Automated Assay” for which the entire contentsare incorporated by reference. A number of procedures in the clinicallaboratory require centrifugation. Examples include clarification ofsamples by removal of sediments or cells and removal of interferingproteins by specific precipitating reagents. In such cases the desiredsupernatant solution is normally decanted from the centrifuge tube to aclean tube for further processing. The present invention allows completephysical separation of the precipitate and supernatant solution in asingle tube so that the supernatant solution can further be treated orsampled as by pipetting without disturbing the precipitate.

Hydrolytic enzymes can be measured by their action on insolublesubstrates or soluble substrates that can be precipitated and separatedfrom soluble products of hydrolysis. These assays can be performed invessels of the present invention with fewer steps and/or reagents thanis customarily used.

The reaction vessel shown in the patent may optionally be fabricated tocontain a longitudinally extending divider within the interior of thebottom of the vessel. This divider will provide the interior of thevessel with a left reagent chamber and a right reagent chamber. Whenusing this alternative form of Vessel 1, it is possible to place a firstreactant in one reagent chamber and a second reactant in the secondreagent chamber without causing interaction between the reagents. Thereaction may then be started by tilting the vessel to allow the reagentsin each chamber to mix, or by rapidly spinning the vessel about itslongitudinal axis thereby causing the reactants to flow upward along theinside walls of the vessel and to mix during the spinning process.

The vessel 1 contains a collection chamber portion located near theuppermost portion of the vessel. This chamber is formed by an increasein their interior diameter of the vessel between two outwardly extendingshoulders.

In a contemplated use by the inventors, the reaction vessel will act asa centrifuge tube spun about it longitudinal axis. If so spun, thecontents will be forced towards the wall of the vessel be centrifugalforce. As the vessel is tapered from a smaller lower diameter to a lowerdiameter to larger upper diameter the centrifugal force can be separatedinto two vectors: the major vector perpendicular to the vessel wall anda smaller vector in the upward direction parallel to the vessel wall. Ifthe latter force exceeds one gravity the tube contents will betransferred entirely to the upper cylindrical portion of the vesselwhere the heavier solids contained in the fluid will be deposited on thevessel wall. If the upward force vector is less than one gravity thevessel contents will remain entirely in the lower portion, assuming thevessel has not been overfilled.

The amount of centrifugal force required to exceed one gravity in thevertical direction is related to the degree of taper in the mid-portionof the vessel, the greater the taper the greater the vertical forcevector and the less total centrifugal force required. The centrifugationspeed required to achieve that centrifugal force is inversely related toachieve that centrifugal force is inversely related to the diameter ofthe vessel according to the following formula: rcf=5.585 d(rpm/1000)².

Pahuski et al. were awarded U.S. Pat. No. 5,700,645 on Dec. 23, 1997entitled “Methods and kits for separation, concentration, and analysisof cells” for which the entire contents are incorporated by reference.

Nielsen et al. were awarded U.S. Pat. No. 4,511,349 on Apr. 16, 1985entitled “Ultracentrifuge Tube with Multiple Chambers” for which theentire contents are incorporated by reference.

A patent was awarded to Glover et al. entitled “Vacutainer with PositiveSeparation Barrier” U.S. Pat. No. 3,879,295 in 1975, for which theentire contents are incorporated herein by reference. Glover teachesthat an improved device for separating serum from cells preferablyembody or provide a number of desirable attributes e.g., (1) obtaining asample of blood and achieving separation of the two phases under sterileconditions; (2) minimizing the risk of loss of identity of the donor;(3) minimizing the migration of cells once the blood has been stratifiedinto cells and serum; (4) utilizing, storing, or transporting the serumwithout interplay between the serum and the cells; (5) economicfeasibility in manufacturing a disposable device; (6) the abilityphysically separate the container at a particular location determinableby the purpose of the test; (7) rapidity and simplicity in inserting thephysical barrier to separate the serum from the cells.

SUMMARY OF THE INVENTION

With this invention a vessel is provided for use in a centrifuge whichutilizes unique geometry to enable more rapid separation of the sampleinto fractions of different densities and to maintain such fractionseparation after centrifugation. The vessel includes an interior spacecontained within an outer wall. A barrier divides this interior space ofthe vessel into at least two regions. These two regions are joinedtogether over a top of a lip of the barrier defining an uppermostportion of the barrier, so that the two regions come together on anupper portion of the vessel but are spaced from each other on a lowerportion of the vessel.

The vessel has a higher gee side and a lower gee side, respectivelydefined by the portion of the vessel most distant from a spin axis ofthe centrifuge and closest to the spin axis of the centrifuge, when thevessel is positioned within a cradle or other vessel support of thecentrifuge. The barrier is oriented to divide the interior space of thevessel into the higher gee region and the lower gee region. Thus, aftercentrifugation is complete, and spinning of the centrifuge stops, higherdensity fractions remain on a higher gee side of the barrier with lowerdensity fractions remain on the lower gee side of the barrier.

Furthermore, sample separation can be enhanced and accelerated byproviding a face of the barrier closest to the spin axis with a taper.This taper is selected so that portions of the face closest to the lipare most distant from the spin axis with portions of the face mostdistant from the lip closest to the spin axis. This taper can be flat orcurving, such as a concave curve, with different contours on the faceadjusting the separation rate.

The vessel benefits from being configured for the specific sample to beseparated. In particular, the lip of the barrier can be positionedand/or the region volumes selected to match expected percentageconstituents of each fraction within the sample. This correlation can beexact or merely general in nature. With such vessel optimization, thebarrier maintains separation of the fractions from each other after thecentrifuge stops spinning for easier and more complete measurement,collection or other post separation processing.

In one embodiment the centrifuge is configured so that the vessel isoriented upright during centrifugation. In such an embodiment thebarrier could be generally vertical with the face and side opposite theface being tapered slightly from vertical. Preferably, the face tapersso that the barrier has a greater horizontal width where spaced from thelip than the horizontal width at the lip. This taper can be flat orconcave, or other shapes to optimize separation.

In a second embodiment, the centrifuge is configured to support thevessel at an angle away from vertical at least somewhat with upperportions of the vessel closer to the spin axis than lower portions ofthe vessel. In such a centrifuge, the barrier has a face which istapered at an angle which causes the tip of the barrier to be furtherfrom the spin axis than portions of the face spaced from the tip. Withsuch a configuration, higher density fractions of the sample can overtime migrate up the face of the barrier, over the lip and into the catchbasin. Similarly, lower density fractions which might begin within thehigher density region of the centrifuge can migrate up over the lip ofthe barrier and into the lower density region of the centrifuge,provided that the density of the particulate fraction is less than thedensity of the suspending fluid.

For certain separations where higher density fractions are present inrelatively small overall percentages of the sample, the higher densityregion on the higher density side of the barrier benefits from beingconfigured to have a small volume similar to but slightly more than anexpected percentage for the higher density fraction of the sample. Inthis way, a relatively small higher density fraction fills a majority orat least a relatively large minority of the higher density region of thevessel. The higher density fractions of the specimen can then berelatively easily distinguished from the higher density region afterspinning of the centrifuge has ceased.

The vessel can be configured with inlet and outlet tubes which accessregions on opposite sides of the barrier. These tubes are utilized forintroduction of the sample into the vessel and for removal of higher andlower density fractions from the vessel after centrifugation.

OBJECTS OF THE INVENTION

Accordingly, a primary object of the present invention is to provide avessel for use in a centrifuge which keeps differing density fractionsof a sample separate after centrifugation.

Another object of the present invention is to provide a centrifugationvessel which facilitates more rapid separation of differing densityfractions therein.

Another object of the present invention is to provide a centrifugationvessel which collects at least some differing density fractions of asample within a defined space to be more readily measured, removed orotherwise analyzed or processed.

Another object of the present invention is to provide a centrifugationvessel which is customized for the separation of a particular sampleinto expected fractions.

Another object of the present invention is to provide a centrifugationvessel optimized for separation of a biological sample into at least twofractions of differing densities.

Another object of the present invention is to provide a method forseparation of a sample into differing density fractions which also keepsthe differing density fractions separate after separation.

Another object of the present invention is to provide a method for morerapidly separating a sample into differing density fractions.

Another object of the present invention is to provide a method forseparating and collecting a fraction of a sample after centrifugation.

Another object of the present invention is to provide a centrifuge whichseparates and collects fractions of different densities from a sample.

Another object of the present invention is to provide a method andapparatus for separating particulate containing fluids into at least twodiffering density fractions without the need for any moving parts, toenhance operational reliability.

Other further objects of the present invention will become apparent froma careful reading of the included drawing figures, the claims anddetailed description of the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a full sectional elevation view of a prior art centrifuge andsample tube supported therein and illustrating prior art separation offractions of the sample.

FIG. 2 is a front elevation full sectional view of that which is shownin FIG. 1 after rotation of the centrifuge has stopped and illustratinghow separated fractions transition to a bottom of the tube aftercentrifugation.

FIG. 3 is a front elevation full sectional view of a centrifuge andcentrifuge vessel according to a first embodiment of this invention witha barrier therein for separate collection of differing densityfractions.

FIG. 4 is a front elevation full sectional view of an alternativeembodiment of that which is shown in FIG. 3 with a barrier exhibiting aconcave face rather than a flat face.

FIGS. 5-9 are full sectional front elevation views of a prior art tubeundergoing centrifugation in a centrifuge having a cradle which isangled to cause upper portions of the tube to be closer to a spin axisof the centrifuge than lower portions of the tube, and illustratingseparation of differing density fractions according to the prior art forsuch centrifuges.

FIG. 10 is a perspective exploded parts view of the centrifuge vessel inthe form of a tube preferred for certain forms of biological sampleseparation.

FIG. 11 is a full sectional front elevation view of that which is shownin FIG. 10.

FIG. 12 is a full sectional front elevation view of that which is shownin FIG. 10 with supply and withdrawal tubes removed and illustrating avariation where a higher density fraction collection region is enlargedby featuring a beveled lower end wall.

FIGS. 13-18 are front elevation views of a series of steps associatedwith separation and collection of various fractions of a biologicalsample according to a method of this invention, with some of the figuresshowing the preferred tube in conjunction with a syringe or supply of asample or removal of fractions from the tube, and some of the viewsshowing the centrifuge operating on the tube for centrifugation of thesample therein.

FIGS. 19-21 are front elevation full sectional views of the tube of FIG.10 and illustrating how different biological samples can locatediffering density fractions thereof in different locations depending onthe characteristics of the sample, such as the hematocrit level of ablood sample.

DESCRIPTION OF THE PREFERRED EMBODIMENT

Referring to the drawings, wherein like reference numerals representlike parts throughout the various drawing figures, reference numeral 110is directed to a preferred tube (FIGS. 10-12) for use in a centrifuge(FIGS. 15 and 16) to separate a sample K (FIGS. 13 and 14) intodiffering density constituents D, G, E (FIGS. 16-18) for separatecollection and removal. By supplying a barrier such as a dam 120 (FIGS.11 and 12) within a vessel, such as in the form of the tube 110, higherdensity fractions D of the sample K are caused to migrate through aspillway 140 from a reservoir 130 to a catch basin 150 for separatecollection, facilitating later convenient and precise removal of variousdifferent fractions of the sample.

In essence, and with particular reference to FIGS. 10-12, basic detailsof the preferred tube 110 providing a preferred form of centrifugationvessel for biological sample separation, are described. The tube 110 isconfined by an outer wall 112 and includes a dam 120 as a preferred formof barrier dividing an interior of the tube 110 into two separateregions. These regions are defined in the preferred embodiment as areservoir 130 and a catch basin 150. A spillway 140 joins the tworegions together over a top of the dam 120. A size of the two regionscan be customized to correlate with expected prevalence of differingdensity fractions within a sample. The dam 120 has a face 122 which isparticularly angled to allow migration of higher density fractions upthe face 122 and through the spillway 140 into the catch basin 150, andto accelerate such separation. The dam 120 maintains separation evenafter the centrifuge ceases spinning. The configuration of the dam 120or other barrier within the tube 110 or other centrifuge vessel can beadjusted for differing types of centrifuges and for use in separation ofdifferent samples and to facilitate different rates of separation anddegree of completeness of separation.

More specifically, and with particular reference to FIGS. 1 and 2, basicdetails of prior art centrifuges to which this invention is animprovement, are described. A most basic prior art centrifuge includes avertical spin axis A with a cradle C configured to support a tube T inan upright fashion extending vertically up out of the cradle C. Thesample within the tube T initially fills the tube T up to an initialfluid line B (FIG. 1). When the centrifuge begins to spin (about thespin axis A) a centrifugal force H (FIG. 1) acts laterally upon thesample within the tube T.

Through the effects of higher gee forces upon the sample, higher densityfractions of the sample migrate further from the spin axis A leavinglower density fractions of the sample closer to the spin axis A. Suchhigher density fractions D are illustrated by darker shading relative tolower density fractions E depicted by lighter shading. A boundary F islocated between the higher density fraction D and the lower densityfraction E with this boundary F defining a transition between these twodensities of fluids. A certain amount of time is involved depending onthe speed at which the centrifuge rotor rotates and the distance thatthe cradle C is located away from the spin axis A, and a differential inthe densities of the fractions being separated (and other fluidcharacteristics). Depending on the purposes of the separation, it may besufficient to only partially separate the sample into differing densityfractions, or a greater degree of completeness of separation may bepursued, such as by operating the centrifuge for a longer period of timeor changing the geometry of the centrifuge.

One problem with prior art centrifugation using angular and verticalrotors is illustrated in FIG. 2. To measure, remove or otherwise act onfractions of the sample, the centrifuge is typically stopped fromspinning. This causes the higher density fraction D to migrate to abottom of the tube T with the lower density fraction E migrating to anupper portion of the tube T. Such migration takes place over a period oftime as the centrifuge slows to a stop. Depending on the nature of thefluid and the difference in the densities between the fluid, and thespeed and smoothness with which the centrifuge decelerates to astandstill, some degree of remixing of the fractions tends to occur,such that the boundary is less clearly defined. Measuring, separationand other action on different fractions of the sample is thus made morecomplex. With such complexity, a greater amount of skill is required foraction on different fractions of the sample.

With particular reference to FIG. 3, basic details of a basic tube 10according to a first embodiment of this invention is described. In thisembodiment, the tube 10 acts as a form of centrifuge vessel whichresides within the cradle C of the centrifuge vertically similar to theprior art (FIGS. 1 and 2). Uniquely, the tube 10 includes a dam 20 whichacts as a barrier extending up from a floor 14 of the tube 10. This dam20 is typically fixed within the tube 10. An outer wall 12 of the tube10 defines an interior space of the tube 10 which is divided by the dam20 into two regions. These regions are referred to as a reservoir 30 anda catch basin 50. Portions of the interior space of the tube 10 abovethe dam 20 are referred to as a spillway 40 where the two regions cometogether. A stopper 16 is typically provided to contain the samplewithin the tube 10 during centrifugation.

The dam 20 can have a variety of different configurations. In a simplestconfiguration, the dam 20 could merely be a generally vertical wall ofnearly constant thickness extending up from the floor 14. Mostpreferably, the dam 20 includes a face 22 which tapers at an angle downfrom a lip 24 adjacent the spillway 40, the lip 24 defining a portion ofthe dam 20 most distant from the floor 14. By angling the face 22,separation is enabled and a rate at which separation occurs can beaccelerated. Also, a relative volume of the two regions is adjusted.

In this embodiment, the catch basin 50 has a constant width away from ahigher gee side of the tube 10. This width of the catch basin 50 isconfigured to be small when a higher density fraction D makes up a smallportion of the overall sample, and this catch basin 50 can be providedwith a greater width and hence a greater volume if the higher densityfraction D has a greater proportion of the overall sample. Such matchingof the width of the catch basin 50 and the position of the dam 20 orother barrier within the tube 10 can be precise or merely approximate,to meet the design objectives of the user.

Initially, the sample resides within the reservoir 30, and optionallypartially within the catch basin 50. During centrifugation, this samplemigrates against the higher gee portion (that portion most distant fromthe spin axis of the centrifuge when the tube 10 is within the spinningcentrifuge 2, and the corresponding opposite side being referred to asthe “lower gee side”) of the outer wall 12 of the tube 10, such that thecatch basin 50 is filled with fluid and the reservoir 30 is onlypartially filled, with fluid extending over the dam 20 and within thespillway 40 region. The dam 20 can vary in height. In some instanceswhere a small initial sample is being separated, the dam 20 might extendas little as five percent of the way from the floor of the tube 10 up toa top of the tube 10. In other embodiments, the dam 20 might extend upto ninety-nine percent of a height of the tube 10.

As separation occurs, a surface of the sample is defined by line J (FIG.3) with a boundary between fractions of differing density is establishedas line I (FIG. 3). Then, when the centrifuge ceases operation, andslows to a stop, the higher density fluid D remains within the catchbasin 50 and the lower density fraction E falls down into the reservoirE. The separation of the differing density fluids is thus maintainedeven after the centrifuge has stopped rotating. This is in contrast tothe less precise boundary F (FIG. 2) provided by the prior art.Furthermore, collection can be made more precise, and less complex inthat collection of higher density fluid D merely involves extractionfrom the catch basin 50.

In FIG. 4, an alternative to the tube 10 of FIG. 3 is depicted, in theform of tube 60. This alternative tube 60 includes an outer wall 62extending up from a floor 64 and with the alternative tube 60 closed bya stopper 66. Such details are similar to those of the tube 10 (FIG. 3).In this embodiment, an alternative dam 70 is provided which uniquelyexhibits a concave face 72 which has a concave curving taper from thefloor 64 up to a lip 74, defining an uppermost portion of thealternative dam 70. The alternative dam 70 divides a reservoir 80 from acatch basin 100 with a spillway 90 joining reservoir 80 and catch basin100 together.

Operation of the alternative tube 60 within a centrifuge occurs similarto the operation described above with respect to the tube 10 (FIG. 3).However, because the alternative dam 70 has a concave face 72,separation of the higher, density fraction can occur more rapidly. Inparticular, note that as the face 72 transitions towards the tip 74, asteeper angle is presented by the face 72, so that a greater and greaterforce is required to cause the higher density fraction to migrate overthe tip 74 and into the catch basin 100. However, as the higher densityfraction D moves closer to the higher gee wall of the tube 60, greaterand greater forces are acting on the higher density fluid D to drive thehigher density fluid D over the tip 74. With such a concave contour forthe face 72, these characteristics are optimized for rapid separation.

With particular reference to FIGS. 5-9, details of a prior art tube T′for use in a cradle C′ of a centrifuge exhibiting an angled cradle C′are described. In this prior art centrifuge, the cradle C′ is angled(FIG. 6) so that the upper end of the tube T′ is closer to the spin axisA at a lower portion of the tube T′ which resides within the cradle C′.An initial fluid line B for a sample K remains horizontal beforespinning of the centrifuge, with such horizontal fluid line B parallelwith the floor before placement in the centrifuge and then angledrelative to the floor and non-perpendicular to outer walls of the tubeT′ after placement within the cradle C′ (FIGS. 5 and 6).

When the centrifuge begins to spin (about spin axis A (FIG. 7))centrifugal forces acting along arrow H (FIG. 7) cause this initialfluid line B to be angled to approximately vertical. Centrifuges areallowed to continue to spin at a sufficiently high rate to cause thehigher density fraction D to migrate further from the spin axis A,displacing a lower density fraction E toward the spin axis A. In therepresentation depicted in FIG. 8, a mid-density fraction G is alsoseparated which migrates to a location between the higher densityfraction D and the lower density fraction E. One such sample K is abiological sample which includes higher density fractions D in the formof “pellet” material and lower density fluid E in the form of plasma andmid-density fluid G is in the form of a “buffy coat.”

Once separation is complete, the centrifuge is decelerated to a stop sothat the final position of the fluids within the tube T′ are similar tothat depicted in FIG. 9. Note that depending on the characteristics ofthe biological sample, it can be difficult to maintain full separation.As the various density fractions migrate from their position duringcentrifugation (FIG. 8) and after stopping of the centrifuge (FIG. 9) anopportunity is presented for remixing of the various different fractionsto some extent. As depicted in FIG. 9, a boundary F′ can tend to absorbinto the mid-density fraction G making this mid-density fraction Gdifficult to identify, measure or extract.

Even if the separation remains complete, if the mid-density fluid is arelatively small proportion of the overall sample, extraction can berather difficult in that an extraction tube must be carefully placed ata depth precisely within such a mid-layer without being too deep or tooshallow. Such procedures typically require skilled personnel and are nothighly amenable to automation and high reliability processing, unlessexceptional care is taken to ensure that the proper fraction is beingextracted from the tube T′.

With particular reference to FIGS. 10-12, details of a preferred tube110 for use in separating fractions from a sample K such as a biologicalsample are described. This tube 110 provides the preferred form ofcentrifuge vessel for certain forms of separations. Variations on thispreferred tube 110 can be made to accommodate samples having differentfraction constituent percentages, or for separations which havefractions which have a greater or lesser density differential from eachother, or for separations which are optimized for completeness ofseparation or optimized for speed, or optimized for simplicity of thecentrifuge vessel, or optimized for other parameters defined by theuser.

With this preferred tube 110, an outer wall 112 defines an interiorspace of the tube 110. This outer wall 112 is preferably cylindricalwith a circular cross-section, but could have other contours. The outerwall 112 extends up from a floor 114 to an upper end which is enclosedby a cap 116. With this preferred tube 110, access into an interior ofthe tube 110 occurs through the cap 116. In particular, an in port 117is supplied for accessing one side of an interior of the tube 110 and anout port 118 is provided for accessing of an opposite side of aninterior of the tube 110. An air port 119 is optionally provided toallow for removal of air or other fluids contained within the tube 110during introduction of a sample to be separated. If required, a checkvalve or other filter 115, such as an anti-microbial filter can beassociated with the air port 119 to prevent leakage or contaminationfrom the air port 119 during centrifugation. As an alternative, the tube110 could be initially filled with a vacuum, so that no such air port119 would be required. As another alternative, air could be removedthrough one of the ports 117, 118 while a sample is introduced into thetube 110 through the other of the ports 118, 117.

The tube 110 includes a barrier therein which separates an interior ofthe tube 110 into two regions including a lower gee region locatedcloser to a spin axis A (FIG. 16) of the centrifuge and a higher geeregion located further from the spin axis A of the centrifuge. Thisbarrier is preferably in the form of a dam 120 with the two regionsdefined as a reservoir 130 closer to the spin axis A (FIG. 16) and acatch basin 150 on a side of the dam 120 further from the spin axis A. Aspillway 140 joins the reservoir 130 and catch basin 150 together overthe dam 120.

The dam 120 could conceivably be a planar structure of constantthickness. With such a configuration, the dam 120 would be angled at anangle matching an angle of the cradle C′ (FIGS. 15 and 16) so that thisdam 120 would have approximately vertical sides when undergoingcentrifugation.

Most preferably, the dam 120 has a non-uniform width with a narrowestportion of the dam 120 at a lip 124 adjacent the spillway 140 and mostdistant from the floor 114. This dam 120 has a face 122 facing thereservoir 130 which tapers non-parallel to the inner surface of theouter wall 112 and non-perpendicular to the floor 114. The taper can beflat as depicted in FIGS. 11 and 12, or can be concave (similar to FIG.4) or exhibit other contours.

The angle of the face 122 is selected so that the lip 124 of the dam 120is further from the spin axis A than any other portions of the face 122.This angle of the face 122 away from vertical measures greater than zerodegrees and the tube 110 has operated successfully with the face 122angle being five degrees. While a range from one to ten degrees isconsidered optimal, face 122 angles up to about thirty degrees may beeffective in some cases. With such a configuration, higher densityfractions within a sample can migrate up along the face 122 up to thelip 124, through the spillway 140 and into the catch basin 150. As canbe seen, if the face 122 tapered so that the lip 124 was closer to thespin axis A than other portions of the base 122, higher densityfractions would become trapped within the reservoir 130 and fullseparation would be frustrated.

A surface of the dam 120 opposite the face 122 benefits in thisembodiment from being substantially parallel with the outer wall 112.Furthermore, the catch basin 150 is preferably rather thin so that thecatch basin 150 has a smaller volume than the reservoir 130. Suchsmaller volume is particularly beneficial when the sample beingseparated has a higher density fraction D (FIG. 6) which makes up asmaller proportion of the sample K (FIG. 14) than the lower densityfraction E.

The reservoir 130 includes a supply tube 132 extending thereinto throughthe cap 116. The supply tube 132 extends down to a tip 133 from whichfluids can be directed into the reservoir 130. A plug 134 is providedfor plugging the supply tube 132 outside of the cap 116, such as toprevent discharge of fluids during centrifugation. While the supply tube132 is coupled to the in port 117 in the cap 116, the supply tube 132could be used for both introduction and removal of fluids from withinthe tube 110.

In one embodiment a withdrawal tube can be configured to include acurving lower tip so that it withdraws a fraction primarily from above abottom end of the tip. If the tip faces down, a false floor deflectionplate can be fitted on the catch basin so that withdrawal ofconstituents above such a false floor does not capture constituentsbelow the false floor. Such a withdrawal tube can be particularlyeffective in extracting a medium density constituent, such as a “buffcoat,” platelet rich plasma or a stromal vascular fraction from adiposetissue.

The catch basin 150 includes the withdrawal tube 152 extending down fromthe cap 116 and in communication with the out port 118. The withdrawaltube 152 extends down to a tip 153. This tip 153 is preferably in alower half of the catch basin 150 and most preferably directly adjacentto the floor 114, with only sufficient space to prevent blocking of thetip 153. A plug 154 can be provided for closing off the out port 118,such as to prevent leakage from the tube 110 during centrifugation.While the withdrawal tube 152 and out port 118 are primarily used forremoval of fractions after centrifugation, these structures couldsimilarly be utilized for introduction of fluids into the tube 110.

The catch basin 150 benefits from having a constant width and dimensionswhich make it significantly elongated with a height many times greaterthan its width. In this manner, a relatively small higher densityfraction D (FIGS. 16 and 17) can be more easily discerned and measured.Furthermore, the precise positioning of a tip 153 of a withdrawal tube152 within a fraction to be removed can more effectively occur when thecatch basin 150 has such an elongate geometry.

In one embodiment, where it is desirable that the catch basin 150 tohave a larger volume, a lower end of the catch basin 150 is providedwith a beveled lower end wall 155 (FIG. 12). In such an embodiment, arelatively narrow upper portion of the catch basin 150 can still beprovided for precise measurement and collection of mid-density fractionsG when the sample has a relatively large amount of higher densityfraction D and lower density fraction E, by locating the mid-densityfraction G within the narrower upper portion of the catch basin 150.With such a beveled lower end wall 155, an angle of this beveled lowerend wall is carefully selected so that lower portions of this end walladjacent the floor 114 are further from the spin axis A than upperportions of this beveled lower end wall 155. In such a way, any lowerdensity fraction E beginning within a bottom of the catch basin 150 canmigrate up to the catch basin 150 and over the spillway 140 into thereservoir 130 during centrifugation, rather than trapping lower densityfractions within the catch basin 150.

With particular reference to FIGS. 13-18, details of a method ofseparating a sample A into differing density fractions, and particularlya biological sample having a higher density fraction “pellet” D, a lowerdensity fraction E and a mid-density “buffy coat” fraction G aredescribed. This method is utilized for the preferred tube 110 in a mostpreferred form of this method, but could similarly operate with othertubes 110. Initially, a syringe S or other source of sample K is coupledto the in port 117 and the sample K is inputted into the reservoir 130.The sample K can be sufficiently large that some portions of the sampleK also initially migrate into the catch basin 150.

The tube 110 is then placed within the cradle C′ of a centrifuge. Plugs134, 154 are placed within the in port 117 and out port 118 to keep thesample K contained within the tube 110 (FIG. 15). The centrifuge is thencaused to spin about the spin axis A (FIG. 16). Initially, the sample Kis still homogenous and migrates to completely fill the catch basin 150and only partially fill the reservoir 130. Because the taper of the face122 is such that the lip 124 on the dam 120 is further from the spinaxis A then other portions of the face 122, higher density fraction Dportions of the sample K migrate up the face 122, over the lip 124,through the spillway 140 and into the catch basin 150. Similarly, lowerdensity fractions E that originally start within the catch basin 150 canmigrate up out of the catch basin 150 and over the lip 124 of the dam120, through the spillway 140 and into the reservoir 130.

Such centrifugation continues until separation has been completed to thesatisfaction of the user, and the higher density fraction D is locatedwithin the lower portion of the catch basin 150, with lower densityfraction E fluid contained within the reservoir 130, and possibly upperportions of the catch basin 150. A mid-density fraction G, such as abuffy coat, resides in a mid-portion of the spillway 140. Due to athinness of the catch basin 150 and elongate form, the buffy coat Gwhich makes up a small percentage of the overall sample K takes up avisually significant readily discernible portion of the catch basin 150for ready measurement and collection therefrom.

In particular, the tube 110 is removed and placed upright (FIG. 17). Thevarious different fractions of the sample remain separated by the dam120. The plug 154 on the out port 118 is removed and the syringe Scoupled to the out port 118. Because the withdrawal tube 152 in thisembodiment extends down to a bottom of the catch basin 150, the syringeis used to first extract the higher density “pellet” portion of thebiological sample. This causes the mid-density fraction G “buffy coat”to migrate down to a bottom of the catch basin 150 and portions of thelower density fraction E to also migrate down somewhat within the catchbasin 150. Once all of the higher density fluid D has been removed, thesyringe S can be decoupled from the outport 118 for discharge of thehigher density fraction D from the syringe S for separate collection andpotential use. The syringe S is then re-coupled to the outport 118 andfurther extraction through the withdrawal tube 152 causes collection ofthe mid-density fraction G “buffy coat” of the biological sample forcollection and use.

With such a methodology, samples having somewhat differing prevalence ofdiffering density fractions can be accommodated without requiring thewithdrawal tube 152 to have a precise length which would only besuitable for certain blood characteristics. For instance, with changesin hematocrit levels, a greater or lesser degree of higher densityfraction D “pellet” portions of the biological sample K are present.With the tube 110 configured as depicted in FIGS. 19-21, the buffy coatG remains within the catch basin 150 for all biological samplehematocrit levels. By having the withdrawal tube 152 extend down to thefloor 114, the higher density fraction D is always first removed,followed by the mid-density fraction buffy coat G. In such a manner,similar collection protocols can be utilized for samples havingdiffering characteristics and reliable separation and collection isachieved.

This disclosure is provided to reveal a preferred embodiment of theinvention and a best mode for practicing the invention. Having thusdescribed the invention in this way, it should be apparent that variousdifferent modifications can be made to the preferred embodiment withoutdeparting from the scope and spirit of this invention disclosure. Whenstructures are identified as a means to perform a function, theidentification is intended to include all structures which can performthe function specified. When structures of this invention are identifiedas being coupled together, such language should be interpreted broadlyto include the structures being coupled directly together or coupledtogether through intervening structures. Such coupling could bepermanent or temporary and either in a rigid fashion or in a fashionwhich allows pivoting, sliding or other relative motion while stillproviding some form of attachment, unless specifically restricted.

1-25. (canceled)
 26. A centrifuge vessel, comprising in combination: anupper end and a floor end; an outer wall surrounding a fluid containinginterior space of the vessel, the outer wall extending from the upperend to the floor end; a barrier inside said outer wall, said barrierpartially dividing said interior space into a first region and a secondregion; and said barrier having a lip, with said first and secondregions connected above said lip and said first and second regionsspaced apart by said barrier below said lip, wherein the barrier in thefirst region extends tapering diagonally from the lip to the innersurface of the outer wall at a position between the upper end and thefloor end.
 27. The vessel of claim 26, wherein said barrier is tallerthan half of a height of the vessel with said lip of said barrier at atop of said barrier.
 28. The vessel of claim 26, wherein the secondregion on a side of said barrier opposite said reservoir defines a catchbasin, said dam providing an increasing spacing between said reservoirand said catch basin as said dam extends down from said lip.
 29. Thevessel of claim 28, wherein a taper angle of said face is less than anorientation angle for the vessel when the vessel is located within acradle of a centrifuge, such that during centrifugation portions of saidface adjacent said lip are furthest from a spin axis of said centrifuge.30. The vessel of claim 29, wherein a side of said dam adjacent saidcatch basin is substantially parallel with a portion of said outer walladjacent said catch basin for a majority of a height of said catchbasin.
 31. The vessel of claim 29, wherein said side of said damadjacent said catch basin includes a tapering portion, said taperingportion tapering away from portions of said outer wall adjacent saidcatch basin to increase a width of said catch basin at lower portions ofsaid catch basin, said tapering portion tapering at an angle relative tosaid face of said dam which causes a thickness of said dam between saidtapering portion and said face to be greatest at a lower end of saidtapering portion.
 32. The vessel of claim 26, wherein said lip of saidbarrier is located closer to a highest gee side of the vessel than to alowest gee side of said vessel during centrifugation.
 33. The vessel ofclaim 32, wherein said lip is located a distance away from said highestgee side of the vessel which is correlated to a prevalence of higherdensity fractions of a fluid to be separated from a sample placed withinthe vessel.
 34. A centrifuge and fluid containing vessel, comprising incombination: a spin axis; a centrifuge vessel adapted to contain a fluidwithin an outer wall thereof; at least one cradle adapted to supportsaid centrifuge vessel, said cradle spaced from said spin axis; saidcradle adapted to spin about said spin axis; said centrifuge vesselhaving said outer wall extending from an upper end to a floor endsurrounding a fluid containing interior space of said vessel; and saidvessel including a barrier inside said outer wall, said barrierpartially dividing said interior space into a first region and a secondregion and said barrier having a lip, with said two regions connectedabove said lip and said first and second regions spaced apart below saidlip, wherein the barrier in the first region extends tapering diagonallyfrom the lip to the inner surface of the outer wall at a positionbetween the upper end and the floor end.
 35. The combination of claim34, wherein said cradle has an upper end which is open and into whichsaid centrifuge vessel is adapted to be removably placed along a cradlecenter line, said center line of said cradle oriented substantiallyparallel with said spin axis.
 36. The combination of claim 35, whereinsaid barrier includes a face extending down from said lip on a side ofsaid barrier closest to said spin axis, said face extending at an angletapering toward said spin axis as said face extends away from said lip.37. The combination of claim 38, wherein said face tapers in a curvingmanner away from said lip and partially toward said spin axis as saidface extends away from said lip.
 38. The combination of claim 35,wherein said cradle includes an open upper end into which saidcentrifuge vessel is adapted to be removably placed along a center lineof said cradle, said center line of said cradle angled non-parallel tosaid spin axis with said open upper end of said cradle located closer tosaid spin axis than other portions of said cradle.
 39. The combinationof claim 38, wherein said barrier has a face extending down from saidlip on a side of said barrier closest to said spin axis, said faceangled to be closer to said spin axis where said face is spaced fromsaid lip than a distance from said face to said spin axis where saidface is adjacent said lip.
 40. The combination of claim 39, wherein aside of said barrier opposite said face is oriented substantiallyparallel with portions of said outer wall most distant from said spinaxis for at least a portion of said barrier.
 41. The combination ofclaim 40, wherein portions of a side of said barrier opposite said facetaper at an angle relative to portions of said outer wall of said vesselmost distant from said spin axis, said angle causing tapering portionsof said wall of said barrier opposite said face to be most distant fromsaid spin axis at a location most distant from said lip of said barrier.42. A fluid container for use in a centrifuge, the container comprisingin combination: an upper end and a floor end an outer wall extendingfrom the upper end to the floor end adapted to contain fluids therein; abarrier inside said outer wall, said barrier dividing an interior of thecontainer into at least a first region and a second region; a lipdefining an upper end of said barrier where said at least first andsecond regions join together above said lip; and a pair of surfaces onsaid barrier extending down from said lip on opposite sides of saidbarrier, wherein the barrier in the first region extends taperingdiagonally from the lip to the inner surface of the outer wall at aposition between the upper end and the floor end.
 43. The container ofclaim 42, wherein said two surfaces of said barrier are orientednon-parallel to each other.
 44. The container of claim 42, wherein saidcontainer has a higher gee side and a lower gee side, with said barrierin fixed position therein, and with one of said surfaces of said barriercloser to said lower gee side defined by a tapering face, said taperingface causing said barrier to have a greater width as said barrierextends from said lip.
 45. The container of claim 44, wherein said faceof said barrier is substantially flat.
 46. The container of claim 44,wherein said face of said barrier is concave.
 47. The container of claim42 wherein said lip is located closer to a higher gee side of thecontainer than to a lower gee side of the container.
 48. The containerof claim 42, wherein said outer wall Is substantially cylindrical. 49.The container of claim 42, wherein said container has a higher gee sideand a lower gee side, with said barrier adapted to be adjustablypositioned in a fixed location and with one of said surfaces of saidbarrier closer to said lower gee side defined by a tapering face, saidtapering face causing said barrier to have a greater width as saidbarrier extends from said lip.
 50. The vessel of claim 42, wherein thebarrier in the second region extends from the lip to the floor end ofthe vessel.
 51. The vessel of claim 42, wherein said first region andsecond region have different widths.